Method and system for identifying a potential lead failure in an implantable medical device

ABSTRACT

A method for detecting potential failures by an implantable medical lead is disclosed. The method includes sensing first, second and third signals between at least first and second combinations of electrodes, on the lead; determining whether at least one of the first, second and third signals is representative of a potential failure in the lead and identifies a failure and the electrode associated with the failure based on which of the first, second and third sensed signals is representative of the potential failure. Optionally, when the first and second sensed signals are both representative of the potential failure, the method further includes determining whether the first and second sensed signals are correlated with one another. When the first and second sensed signals are correlated, the method declares an electrode common to both of the first and second combinations to be associated with the failure.

RELATED APPLICATIONS

This application claims the benefit of U.S. Provisional Application Ser.No. 61/783,780, filed Mar. 14, 2013, and is a continuation-in-part ofU.S. patent application Ser. No. 12/498,982, filed Jul. 7, 2009, titled“METHOD AND SYSTEM FOR IDENTIFYING A POTENTIAL LEAD FAILURE IN ANIMPLANTABLE MEDICAL DEVICE,” now U.S. Pat. No. 8,391,980, the completesubject matter of which is expressly incorporated herein by reference inits entirety.

FIELD OF THE INVENTION

Embodiments of the present invention generally pertain to implantablemedical devices and more particularly to methods and systems thatidentify potential lead failures in the devices and take correctiveaction based thereon.

BACKGROUND OF THE INVENTION

An implantable medical device (IMD) is implanted in a patient tomonitor, among other things, electrical activity of a heart and todeliver appropriate electrical therapy, as required. Implantable medicaldevices include pacemakers, cardioverters, defibrillators, implantablecardioverter defibrillators (ICD), and the like. The electrical therapyproduced by an IMD may include pacing pulses, cardioverting pulses,and/or defibrillator pulses to reverse arrhythmias (e.g., tachycardiasand bradycardias) or to stimulate the contraction of cardiac tissue(e.g., cardiac pacing) to return the heart to its normal sinus rhythm.

Electrodes coupled to leads are implanted in the heart to sense theelectrical activity of the heart and to deliver electrical therapy tothe heart. The electrodes communicate the electrical activity as cardiacsignals to the IMD via the leads. The electrodes may be placed withinthe chambers of the heart and/or secured to the heart by partiallyinserting the electrodes into the heart. The cardiac signals sensed bythe electrodes are used by the IMD to deliver appropriate pacing therapyand/or stimulation pulses, or “shocks” to the heart.

A lead failure occurs when an electrode fails. The electrodes may failand no longer be capable of accurately sensing and communicating cardiacsignals to the IMD. Known lead failures involve electrodes fracturing,breaking or becoming dislodged from the myocardium. Lead failures canresult in increased noise in the cardiac signals communicated to theIMD. With respect to fractured electrodes, the noise may be caused bythe fractured components of the electrode rapidly making and breakingcontact with one another at the fracture site. This type of noise may bereferred to as chatter noise.

Lead failures can result in an IMD applying unnecessary or incorrectpacing or stimulation pulses to the heart. For example, if chatter noiseoccurs at a sufficiently high rate, the IMD may misclassify the rate ofthe chatter noise as a tachycardia or fibrillation, such as ventriculartachycardia (VT) or ventricular fibrillation (VF). The IMD may thenerroneously apply pacing or stimulation pulses to the heart. Suchunnecessary pacing and stimulation pulses can cause significantdiscomfort to patients.

Systems have been proposed to detect lead failures based on certainparameters such as differences in R to R intervals, high impedance,impedance trends and slew rate. However, prior detection systems do notidentify which individual electrode(s) is associated with a leadfailure. Nor do prior detection systems offer robust solutions tomitigate failures in sensing electrodes.

Early detection of lead failures and the locations of the lead failuresis desired. Early detection and notification of a lead failure mayenable the patient's physician to reconfigure the IMD to avoid using thefailed electrode. Alternatively, the physician may otherwise adjusttreatment of a patient until the failed lead can be replaced. Knownmethods of detecting lead failures may not accurately detect a locationof the lead failure. That is, while the method may be able to determinethat a lead failure has occurred, the methods do not provide thepatient's physician with a location of the failure, such as anidentification of the electrode on the lead that has failed.

A need exists for a method and system that identifies a potential leadfailure in an IMD and the location of the failure. As the application ofstimulation and pacing pulses to a patient's heart largely depends onthe accurate sensing of cardiac signals, detecting failed leads mayavoid continued sensing using the failed leads. Additionally, earlierdetection of failed leads may permit physicians to reconfigure operationof the IMD to avoid continued use of the failed leads until the leadscan be replaced.

BRIEF SUMMARY OF THE INVENTION

In one embodiment, a method for detecting potential failures by a leadof an implantable medical device is provided. The method includessensing a first signal over a first channel between a first combinationof electrodes on the lead and sensing a second signal from a secondchannel between a second combination of electrodes on the lead. Themethod determines whether at least one of the first and second signalsis representative of a potential failure in the lead and identifies afailure and the electrode associated with the failure based on which ofthe first and second sensed signals is representative of the potentialfailure. Optionally, when the first and second sensed signals are bothrepresentative of the potential failure, the method further includesdetermining whether the first and second sensed signals are correlatedwith one another. When the first and second sensed signals arecorrelated, the method declares an electrode common to both of the firstand second combinations to be associated with the failure.

In another embodiment, an implantable medical device is provided. Thedevice includes a lead, a channel selection module and a failuredetection module. The lead includes electrodes configured to bepositioned within a heart and capable of sensing cardiac signals todetermine a first signal over a first channel between a firstcombination of the electrodes and a second signal over a second channelbetween a second combination of the electrodes. The channel selectionmodule is configured to control which of the electrodes are included inthe first and second combinations of electrodes. The failure detectionmodule determines whether at least one of the first and second signalsis representative of a potential failure in the lead. The failuredetection module also identifies a failure and the electrode associatedwith the failure based on which of the first and second sensed signalsis representative of the potential failure. Optionally, the failuredetection module compares at least one of an amplitude, a rate and aslew rate of the first and second signals to a predetermined thresholdrepresentative of a physiologically acceptable limit for thecorresponding one of the amplitude, rate and slew rate. The channelselection module may be configured to enable a different third channelto sense cardiac signals from a third combination of electrodes when afailure is identified by the failure detection module.

In another embodiment, a method is provided for detecting potentialfailures by an implantable medical lead. The method senses a firstsignal over a first channel between a first combination of electrodes onthe lead. The method determines whether the first signal isrepresentative of a potential failure in the lead, obtains a secondaryindicator of heart condition and utilizes the secondary indicator toconfirm an arrhythmia of the heart when the determining operationidentifies the lead to include the potential failure. The secondaryindicator may represent an impedance plethysmography measurementindicative of a stroke volume. The secondary indicator may represent ahemodynamic indicator from one of a pressure sensor located in a heartchamber, a heart sound sensor and a peak endocardial accelerationsensor. The secondary indicator may be obtained from a hemodynamicsensor, where the secondary indicator is tested after the determiningoperation identifies the potential failure based on the first signal,and the secondary indicator is analyzed before delivery of a therapy.The method may further comprise performing additional analysis of aheart, when the secondary indicator is representative of normal sinusrhythm, before delivering a therapy.

In another embodiment, a method is provided for detecting potentialfailures by an implantable medical lead. The method comprises sensingfirst, second and third signals over first, second and third channelsbetween first, second and third combinations of electrodes on the lead;determining whether at least one of the first, second and third signalsis representative of a potential failure in the lead; and identifying afailure and the electrode associated with the failure based on which ofthe first, second and third sensed signals is representative of thepotential failure.

Optionally, the first combination of electrodes includes a ringelectrode and a tip electrode, the second combination of electrodesincludes a coil electrode and the tip electrode, and the thirdcombination of electrodes includes the tip electrode and an SVCelectrode. The method further comprises declaring a failure of first andsecond electrodes of the first and second combinations when the firstand second signals are representative of non-physiologic signals.Optionally, the method further comprises declaring a short circuit statebetween first and second electrodes when the first and second signalsare both representative of non-physiologic signals.

In another embodiment, an implantable medical device is provided. Thedevice comprises a lead configured to be positioned within a heart, thelead including first, second and third combinations of electrodes thatsense first, second and third signals over first, second and thirdchannels; a channel selection module configured to control which of theelectrodes are included in the first, second and third combinations ofelectrodes; and a failure detection module determining whether at leastone of the first, second and third signals are representative of apotential failure in the lead and identifying a failure and theelectrode associated with the failure based on which of the first,second and third sensed signals are representative of the potentialfailure.

Optionally, the failure detection module identifies a tip electrode tobe associated with the failure when the first and second signals arecorrelated with one another and are representative of non-physiologicsignals.

In another embodiment, a method is provided for detecting potentialfailures by an implantable medical lead. The method senses first, secondand third signals between at least first and second combinations ofelectrodes, respectively, on the lead; and determines whether at leastone of the first, second and third signals is representative of apotential failure in the lead. The method senses identifies a failureand the electrode associate with the failure based on which of thefirst, second and third sensed signals is representative of thepotential failure.

In another embodiment, when at least two signals of the first, secondand third sensed signals are both representative of the potentialfailure, while a third signal of the first, second and third sensedsignals is physiologic, determining which two electrodes are distinctlyassociated with the two signals representing potential failure;determining whether the first and second sensed signals are correlatedwith one; and when a short between the at least two signals of first,second and third sensed signals are correlated and utilize a commonelectrode, declaring the common electrode to be associated with thefailure declaring a short between the two electrodes

In another embodiment, the sensing comprises sensing the first andsecond signals over a common channel associated with the firstcombination of electrodes at successive different first and secondpoints in time. Optionally, the sensing may comprise sensing the first,second, and third signals over first, second and third channels betweencorresponding combinations of the electrodes.

In another embodiment, an implantable medical device (IMD), is providedcomprising at least one lead configured to be positioned within a heart,including at least first and second combinations of electrodes; achannel selection module configured to control which of the electrodesare included in at least the first, second and third second combinationsof electrodes; and a failure detection module determining whether atleast one of the first, second and third signals are representative of apotential failure in the lead and identifying a failure and theelectrodes associated with the failure.

The IMD may include a sensor subsystem configured to sense the first andsecond signals over a common channel associated with the firstcombination of electrodes at successive different first and secondpoints in time. The sensor subsystem may be configured to sense thefirst, second, and third signals over first, second and third channelsbetween corresponding combinations of the electrodes.

BRIEF DESCRIPTION OF THE DRAWINGS

The drawings illustrate generally, by way of example, but not by way oflimitation, various embodiments discussed in the present document.

FIG. 1 illustrates an IMD coupled to a heart in accordance with oneembodiment.

FIG. 2 illustrates a block diagram of exemplary internal components ofthe IMD shown in FIG. 1.

FIGS. 3A and 3B illustrate a process for detecting potential failures ofa lead shown in FIG. 1 according to one embodiment.

FIGS. 4A and 4B includes a table displaying information and datarelevant to various types of lead failures identified by the processshown in FIGS. 3A and 3B.

FIG. 5 illustrates examples of physiologic signal waveforms sensed overone or more of the bipolar and integrated bipolar channels in accordancewith one embodiment.

FIG. 6 illustrates examples of non-physiologic signal waveforms sensedover one or more of the bipolar and integrated bipolar channels inaccordance with one embodiment.

FIG. 7 illustrates a block diagram of exemplary manners in whichembodiments of the present invention may be stored, distributed, andinstalled on a computer-readable medium.

FIG. 8 illustrates a sensor subsystem 800 formed in accordance with analternative embodiment.

FIG. 9 illustrates a process 900 for detecting potential lead or channelfailures of the IMD 100 (shown in FIG. 1) with the sensing subsystem 800shown in FIG. 8.

FIGS. 10A and 10B include a table 1000, similar to the Table in FIGS. 4Aand 4B, but with an additional row 1013 and an additional column 1005.

FIGS. 11A and 11B include a table displaying information and datarelevant to various types of closed circuit lead or channel failuresidentified by the process shown in FIG. 12.

FIG. 12 illustrates a process 1200 for detecting potential combinationsor pairs of lead or channel failures of the IMD 100 (shown in FIG. 1)with the sensing subsystem 800 shown in FIG. 8.

FIG. 13 illustrates a sensor subsystem 1300 formed in accordance with analternative embodiment.

DETAILED DESCRIPTION OF THE INVENTION

In the following detailed description, reference is made to theaccompanying drawings which form a part hereof, and in which are shownby way of illustration specific embodiments in which the presentinvention may be practiced. These embodiments, which are also referredto herein as “examples,” are described in sufficient detail to enablethose skilled in the art to practice the invention. It is to beunderstood that the embodiments may be combined or that otherembodiments may be utilized, and that structural, logical, andelectrical variations may be made without departing from the scope ofthe present invention. The following detailed description is, therefore,not to be taken in a limiting sense, and the scope of the presentinvention is defined by the appended claims and their equivalents. Inthis document, the terms “a” or “an” are used, as is common in patentdocuments, to include one or more than one. In this document, the term“or” is used to refer to a nonexclusive or, unless otherwise indicated.

In accordance with certain embodiments, methods and systems are providedfor detecting potential failures of a lead in an implantable medicaldevice. In one embodiment, the systems and methods described hereinprovide for the sensing of cardiac signals over different combinationsof electrodes joined to a lead to identify an electrode associated withthe lead failure.

FIG. 1 illustrates an implantable medical device (IMD) 100 coupled to aheart 102 in accordance with one embodiment. The IMD 100 may be acardiac pacemaker, an ICD, a defibrillator, an ICD coupled with apacemaker, a cardiac resynchronization therapy (CRT) pacemaker, acardiac resynchronization therapy defibrillator (CRT-D), and the like.The IMD 100 may be a dual-chamber stimulation device capable of treatingboth fast and slow arrhythmias with stimulation therapy, includingcardioversion, defibrillation, and pacing stimulation, as well ascapable of detecting heart failure, evaluating its severity, trackingthe progression thereof, and controlling the delivery of therapy andwarnings in response thereto. Alternatively, the IMD 100 may be atriple- or quad-chamber stimulation device. Optionally, the IMD 100 maybe a multisite stimulation device capable of applying stimulation pulsesto multiple sites within each of one or more chambers of the heart 102.

The IMD 100 includes a housing 110 that is joined to several leads 104,106, 108. The leads 104, 106, 108 are located at various locations ofthe heart 102, such as an atrium, a ventricle, or both, to measurecardiac signals of the heart 102. The leads 104, 106, 108 include theright ventricular (RV) lead 104, the right atrial (RA) lead 106, and thecoronary sinus lead 108. Several electrodes are provided on the leads104, 106, 108. The housing 110 may be one of the electrodes and is oftenreferred to as the “can”, “case”, or “case electrode.” The RV lead 104is coupled with an RV tip electrode 122, an RV ring electrode 124, andan RV coil electrode 126. The RV lead 104 may include a superior venacava (SVC) coil electrode 128. The right atrial lead 106 includes anatrial tip electrode 112 and an atrial ring electrode 114. The coronarysinus lead 108 includes a left ventricular (LV) tip electrode 116, aleft atrial (LA) ring electrode 118 and an LA coil electrode 120.Alternatively, the coronary sinus lead 108 may be a quadropole lead thatincludes several electrodes disposed within the left ventricle. Leadsand electrodes other than those shown in FIG. 1 may be included in theIMD 100 and positioned in or proximate to the heart 102.

The IMD 100 senses cardiac signals over predetermined sensing channelson the leads 104-108. A sensing channel is formed by one, two or othercombination of the electrodes 110-128. For example, the electrodes110-128 associated with a channel may include two electrodes provided onthe same lead 104-108 and/or located in the same chamber of the heart102. Alternatively, a channel may include electrodes 110-128 provided ondifferent leads 104-108 and/or located in different chambers of theheart 102. The electrodes used to sense cardiac signals for each channelare electrodes 112-128 primarily positioned inside the heart 102. Usingelectrodes 112-128 within the heart 102 to sense signals over thechannels may reduce the risk of sensing myopotentials, which couldaffect the cardiac signals used to identify potential lead failures. Inone embodiment, a first channel senses cardiac signals using the RV tipelectrode 122 and the RV ring electrode 124. A second channel sensescardiac signals using the RV tip electrode 122 and the SVC coilelectrode 128. The first channel may be referred to as a bipolar channeland the second channel may be referred to as an integrated bipolarchannel. While the discussion herein is in connection with examplebipolar and integrated bipolar channels, the channels may include adifferent combination of electrodes, including one or more of thehousing 110, the LV tip electrode 116, the LA ring electrode 118, the LAcoil electrode 120, and the like.

Optionally, one or more of the leads 104, 106, 108 may include ahemodynamic sensor 117 and/or 119 that obtains a secondary indicator ofheart condition. Alternatively, or in addition, a hemodynamic sensor 115may be provided on a separate lead 113 and located outside, butproximate to, the heart to monitor the heart condition. The sensors 115,117 and 119 may represent one or more of an impedance plethysmographysensor to sense stroke volume, a pressure sensor to sense pressure inone or more chambers of the heart, a heart sound sensor to sense soundsproduced by the heart and an endocardial sensor to sense a peakendocardial acceleration. The signals from sensors 115, 117 and 119 arerepresentative of normal or abnormal sinus rhythm.

FIG. 2 illustrates a block diagram of exemplary internal components ofthe IMD 100. The housing 110 of the IMD 100 includes several inputs toreceive signals measured or sensed by the electrodes 112-128 (shown inFIG. 1). The inputs may include one or more of an LV tip input (VL TIP)200, an LA ring input (AL RING) 202, an LA coil input (AL COIL) 204, anRA tip input (AR TIP) 206, an RV ring input (VR RING) 208, an RV tipinput (VR TIP) 210, an RV coil input 212 and an SVC coil input 214. Theinputs may also include one or more hemodynamic sensor inputs 211 thatare connected to sensors 117 and 119 on one or more of leads 104, 106,108. One or more hemodynamic lead inputs 213 may be connected to one ormore hemodynamic sensors 115 on a separate lead 113. As the names of theinputs 200-214 imply, the inputs 200-214 are electrically coupled withthe corresponding electrodes and sensors 112-128 (shown in FIG. 1). Forexample, the LV tip input 200 may be connected with the LV tip electrode116 (shown in FIG. 1); the LA ring input 202 may connected with the LAring electrode 118 (shown in FIG. 1); the LA coil input 204 may beconnected with the LA coil electrode 120 (shown in FIG. 1); the RA tipinput 206 may be connected with the RA tip electrode 112 (shown in FIG.1); the RV ring input 208 may be connected with the RV ring electrode124 (shown in FIG. 1); the RV tip input 210 may be connected with the RVtip electrode 122 (shown in FIG. 1); the RV coil input 212 may beconnected with the RV coil electrode 126 (shown in FIG. 1); and the SVCcoil input 214 may be connected with the SVC coil electrode 128 (shownin FIG. 1).

The IMD 100 includes a programmable microcontroller 216, which controlsthe operation of the IMD 100 based on sensed cardiac signals. Themicrocontroller 216 (also referred to herein as a processor, processormodule, or unit) typically includes a microprocessor, or equivalentcontrol circuitry, and may be specifically designed for controlling thedelivery of stimulation therapy and may further include RAM or ROMmemory, logic and timing circuitry, state machine circuitry, and I/Ocircuitry. The microcontroller 216 receives, processes, and managesstorage of digitized data from the various electrodes 112-128 (shown inFIG. 1).

The cardiac signals and hemodynamic signals sensed by the electrodes andsensors 112-128 are communicated through the inputs 200-214 to anelectronically configured switch bank, or switch, 232. The switch 232includes a plurality of switches for connecting the desired electrodesand switches 112-128 (shown in FIG. 1) and inputs 200-214 to theappropriate I/O circuits. The switch 232 closes and opens switches toprovide electrically conductive paths between the circuitry of the IMD100 and the inputs 200-214 in response to a control signal 250. Thecardiac signals are then communicated to a sensor subsystem thatincludes an analog-to-digital (A/D) data acquisition system 230, abipolar sensing amplifier 268, or an integrated bipolar sensingamplifier 270. The hemodynamic signals are communicated through the A/Ddata acquisition system 230 to the microcontroller 216. Themicrocontroller 216 may control the sensor subsystem to sense cardiacsignals over a first channel between the RV tip electrode 122 (shown inFIG. 1) and the RV ring electrode 124 (shown in FIG. 1) and over asecond channel between the RV tip electrode 122 and the SVC coilelectrode 128 (shown in FIG. 1). The first channel may also be referredto as the bipolar channel. The second channel may be referred to as theintegrated bipolar channel. The amplifiers 268, 270 each produce adifference between the input cardiac signals and output correspondingdifference signals to the data acquisition system 230.

A control signal 234 from the microcontroller 216 determines when thedata acquisition system 230 acquires signals, stores the signals in amemory 236 via a data/address bus 238, or transmits data to an externaldevice 240 via a telemetry circuit 272. An atrial sensing circuit 242and a ventricular sensing circuit 244 are selectively coupled to theleads 104-108 (shown in FIG. 1) and the electrodes 112-128 (shown inFIG. 1) through the switch 232 for sensing cardiac activity in thechambers of the heart 102 (shown in FIG. 1). Control signals 246, 248from the microcontroller 216 direct output of the atrial and ventricularsensing circuits 242, 244.

The microcontroller 216 may include one or more modules and processorsthat examine the cardiac and hemodynamic signals to identify a potentialfailure in a lead 104-108 (shown in FIG. 1). The microcontroller 216also may include modules and/or processors that enact or performremedial responses or actions to mitigate the lead failure. A channelselection module 264 of the microcontroller 216 determines the sensingand therapy delivery channels. For example, the channel selection module264 determines which combinations of the housing 110 and/or theelectrodes 112-128 (shown in FIG. 1) are included in a particularsensing channel to sense cardiac signals associated with the particularsensing channel. The channel selection module 264 may vary which of thehousing 110 and/or electrodes 112-128 are associated with a channelthrough the control signal 250 to the switch 232. Optionally, only thefirst channel or only the second channel may be used for sensing. Thechannel selection module 264 disables a channel when a lead failureinvolving one of the electrodes 112-128 associated with the channel isidentified by the microcontroller 216. In order to mitigate a leadfailure, the channel selection module 264 may disable sensing over achannel associated with the lead failure and enable a different channelto sense cardiac signals.

A failure detection module 266 determines whether a potential leadfailure exists. For example and as described below, the failuredetection module 266 may identify a potential lead failure based oncardiac signals sensed over the sensing channels. The failure detectionmodule 266 identifies a lead failure and one or more electrodes 112-128that are associated with the failure based on which of the signals fromthe sensing channel(s) are/is representative of the potential failure.

An impedance measuring circuit 218 measures electrical impedancecharacteristics between predetermined combinations of the housing 110and/or the electrodes 112-128 (shown in FIG. 1). The impedance measuringcircuit 218 is enabled by the microcontroller 216 via a control signal220. The impedance measuring circuit 218 may measure a voltage potentialat one or more electrodes 112-128 and/or a voltage potential differencebetween two or more electrodes 112-128. The electrical impedancemeasured may be utilized as a secondary indicator to confirm or reject apotential lead failure. An atrial pulse generator 222 and a ventricularpulse generator 224 each are configured to generate the pacing and/ornon-pacing stimulation pulses to the atrial and ventricular chambers ofthe heart 102 (shown in FIG. 1), respectively. The pulse generators 222,224 are controlled via corresponding control signals 226, 228 from themicrocontroller 216 to trigger the stimulation pulses.

The memory 236 may be embodied in a computer-readable storage mediumsuch as a ROM, RAM, flash memory, or other type of memory. Themicrocontroller 216 is coupled to the memory 236 by the data/address bus238. The memory 236 may store programmable operating parameters andthresholds used by the microcontroller 216, as required, in order tocustomize operation of IMD 100 to suit the needs of a particularpatient. The memory 236 may store data indicative of cardiac andhemodynamic signals sensed by the electrodes 112-128 (shown in FIG. 1).The operating parameters of the IMD 100 may be non-invasively programmedinto the memory 236 through the telemetry circuit 272 in communicationwith the external device 240, such as a trans-telephonic transceiver ora diagnostic system analyzer. The telemetry circuit 272 is activated bythe microcontroller 216 by a control signal 252. The telemetry circuit272 allows cardiac signals, intra-cardiac electrograms, impedancemeasurements, status information, hemodynamic signals and other datarelating to the operation of IMD 100 to be sent to the external device240 through an established communication link 254.

In the case where IMD 100 is intended to operate as an ICD device, theIMD 100 detects the occurrence of a shift in one or more waveforms insensed cardiac signals that indicates an arrhythmia, and automaticallyapplies an appropriate electrical shock therapy to the heart 102 (shownin FIG. 1) aimed at terminating the detected arrhythmia. To this end,the microcontroller 216 further controls a shocking circuit 260 by wayof a control signal 262. The shocking circuit 260 generates shockingpulses of low (up to 0.5 joules), moderate (0.5-10 joules) or highenergy (11 to 40 joules). Such shocking pulses are applied to the heart102 of the patient through at least two shocking electrodes, and asshown in this embodiment, selected from the LA coil electrode 120 (shownin FIG. 1), the RV coil electrode 126 (shown in FIG. 1), and/or the SVCcoil electrode 128 (shown in FIG. 1).

A hemodynamic monitor module 267 collects and analyzes hemodynamicsignals as a secondary indicator of the condition of the heart. When themodule 267 is used, the IMD 100 may identify a potential arrhythmiabased on cardiac signals while the hemodynamic signals indicate that theheart is in normal sinus rhythm. When the foregoing combination ofcontradictory indicators occurs, the IMD 100 may forego or delaydelivery of the shock therapy for at least a supplemental analysisperiod of time. During the supplemental analysis time, an arrhythmiaconfirmation module 269 performs addition confirmation analysis of priorand/or new cardiac and/or hemodynamic signals. The addition analysis mayutilize more robust arrhythmia detection algorithms (cardiac and/orhemodynamic based) that are not readily available for real-timecontinuous use. The addition analysis may review cardiac and/orhemodynamic signals from other chambers of the heart, collection andanalysis of new cardiac and/or hemodynamic signals and the like. The IMD100 may then deliver the therapy after the addition confirmationanalysis, or abort any type of therapy, based on the results of theconfirmation analysis.

A battery 256 provides operating power to the circuits of the IMD 100,including the microcontroller 216. The IMD 100 also includes aphysiologic sensor 258 that may be used to adjust pacing stimulationrate according to the exercise state of the patient.

FIGS. 3A and 3B illustrate a process 300 for detecting potential leadfailures of the IMD 100 (shown in FIG. 1). The process 300 operates todetermine if a lead failure has occurred and, if a lead failure hasoccurred, to identify the electrode(s) associated with the lead failure.The process 300 may continue to operate, after a lead failure, isidentified to determine if any additional lead failures occur. A and 4Binclude a table 400 in which each of the columns 402-408 includesinformation and data relevant to different types of lead states. Eachcolumn 404-408 corresponds to a different type or category of leadstate, such as no fault, failure type 1, etc. The information in FIGS.4A and 4B will be referenced in connection with the following discussionof the process 300 in FIGS. 3A and 3B.

At 302, during the “no fault” operation of the lead 104 (shown in FIG.1), cardiac signals are sensed over the bipolar or first channel andintegrated bipolar or second channel. The first column 402 of the table400 is associated with application of the process 300 when detecting a“no fault” condition of the IMD 100 (shown in FIG. 1), namely where noelectrode failure is detected or identified in a lead. The first row 410illustrates examples of different waveforms sensed by the first channel.The cell at the intersection of the first row 410 and the first column402 illustrates an example of a normal physiologic bipolar waveform 430sensed over the first or bipolar channel during the “no fault” operationof the lead 104. The bipolar waveform 430 in this embodiment representsthe cardiac signals that are sensed using the RV tip electrode 122 andthe RV ring electrode 124. The second row 412 illustrates examples ofdifferent waveforms sensed by the second channel. The cell at theintersection of the second row 412 and the first column 402 illustratesan example of a second or integrated bipolar waveform 436 that is sensedover the integrated bipolar channel during the “no fault” state of thelead 104. The bipolar and the integrated bipolar waveforms 430, 436include, among other things, several R-waves 432 and S-waves 434 thatare indicative of the normal physiologic behavior of the left ventricle.The third row 414 illustrates results that arise from the waveformcombinations in 410 and 412.

In FIG. 3A, at 304, the cardiac signals sensed over the bipolar andintegrated bipolar channels are compared to one another. In oneembodiment, the cardiac rates of the cardiac signals are compared to oneanother. For example, the frequencies at which the R-waves 432 and/orthe S-waves 434 occur over the bipolar and integrated bipolar channelsmay be compared. If the cardiac rates are similar to one another, thenthe similar cardiac rates may be indicative of a normally operating lead104 (shown in FIG. 1) that does not exhibit signs or evidence of apotential lead failure. The cardiac rates may be considered similar toone another when the cardiac rates are within a predetermined thresholdrange of one another over a predetermined time period. For example, thecardiac rates may be determined to be similar if the cardiac rate sensedover the bipolar channel is within 10% of the cardiac rates sensed overthe integrated bipolar channel during the previous 60 seconds or over apredetermined number of cardiac cycles. Alternatively, a differentpercentage range and/or time period may be used.

At 306, if the cardiac rates are found to be similar at 304, the cardiacrates sensed over the bipolar and integrated bipolar channels arecompared to a predetermined rate threshold. The cardiac rates arecompared to the predetermined rate threshold to determine if the cardiacrates are indicative of an abnormal heart rate, such as VT or VF. If thecardiac rates exceed the rate threshold, then the cardiac rates may beindicative of an abnormal heart rate. Alternatively, if the cardiacrates do not exceed the rate threshold or are not otherwise indicativeof an abnormal heart rate, then the process 300 returns to 302. Theprocess 300 may proceed in a loop-wise manner between 302, 304 and 306where no potential lead failure is identified and the cardiac signalssensed over the bipolar and integrated bipolar channels do not exhibitcardiac rates that exceed the rate threshold.

If the cardiac rates are found to exceed the rate threshold at 306, flowmoves to 308 where the cardiac signals are examined to determine if thesignals correspond to physiologic (normal or abnormal) cardiacwaveforms. For example, as shown in FIG. 4A at the cell at theintersection of row 416 and column 402, when a simultaneous orconcurrent high rate is found in the cardiac signals sensed over thebipolar and integrated bipolar channels, a physiologic test may beperformed on the cardiac signals. The signals may be examined todetermine if the signal waveforms have characteristics similar to thoseof normal or abnormal physiologic cardiac waveforms. If the cardiacsignal waveforms are similar to abnormal physiologic cardiac waveforms,then the high cardiac rate sensed over the bipolar and integratedbipolar channels may be due to “natural” causes, such as a cardiaccondition, VT, VF, and the like. Alternatively, if the cardiac signalwaveforms are not similar to normal or abnormal physiologic cardiacwaveforms, then the high cardiac rate sensed over the bipolar andintegrated bipolar channels may be due to an unnatural cause, such aschatter noise resulting from a fractured electrode and the like.

In one embodiment, the physiologic test at 308 involves analyzing valuesof one or more physiologic indicators or parameters of the cardiacsignals sensed over the bipolar and integrated bipolar channels. Thephysiologic indicators may include the cardiac rates, a slew rate, azero crossing rate, and an amplitude of the cardiac signal waveforms.The slew rate represents the slope or rate of change in the cardiacsignal. The zero crossing rate represents the rate at which the cardiacsignal switches between positive and negative voltage potentials. Thevalues of the physiologic indicators may be compared to one another orto predetermined thresholds to determine if the signals are physiologicor non-physiologic. The predetermined thresholds are representative ofphysiologically acceptable limits for corresponding ones of thephysiologic indicators.

FIG. 5 illustrates an example of a physiologic signal waveform 500 thatmay be sensed in accordance with one embodiment. FIG. 6 illustrates anexample of a non-physiologic signal waveform 600 that may be sensed inaccordance with one embodiment. The signal waveforms 500, 600 are shownalongside corresponding horizontal axes 502, 602 that are representativeof time and vertical axes 504, 604 that are representative of theamplitude of the signal waveforms 500, 600.

The cardiac rate of the waveforms 500, 600 may be measured over apredetermined time period to determine if the waveforms 500, 600 arerepresentative of physiologic waveforms. If the cardiac rates do notexceed a predetermined rate threshold, then the cardiac rates mayindicate that the corresponding waveforms 500, 600 are physiologic. Forexample, if the time interval between consecutive ventricularcontractions that is represented by each waveform 500, 600 does notexceed approximately 240 milliseconds, then the corresponding waveform500, 600 may be physiologic (normal or abnormal). In another example, ifthe cardiac rate is approximately constant over the predetermined timeperiod (such as the cardiac rate of the waveform 500), then the cardiacrate may indicate that the corresponding waveform is representative of aphysiologic waveform. Alternatively, if the cardiac rate is notapproximately constant over the time period (such as the cardiac rate ofthe waveform 600), then the cardiac rate may indicate that thecorresponding waveform is not representative of a physiologic waveform.The cardiac rate may be considered at 308 to be approximately constantover a time period when the cardiac rate does not vary outside of apredetermined range or percentage during the time period. For example,the cardiac rate may be considered at 308 approximately constant if thecardiac rate does not vary by more than 10% during the time period.

Slew rates 506, 606 of the waveforms 500, 600 represent rates of changein the waveforms 500, 600. The slew rates 506, 606 may be referred to asthe slope of the waveforms 500, 600. In one embodiment, the slew rate506, 606 is the largest, or maximum, rate of change in the cardiacsignals over the predetermined time period. For example, the slew ratesof the waveform 500 may be approximately the same for the waveform 500over the time period shown in FIG. 5. The slew rates of the waveform 600varies during the time period shown in FIG. 6, with the largest slewrate 606 occurring during the approximately vertical portions of thewaveform 600. The slew rates 506, 606 may be compared to one anotherand/or to a predetermined slew rate threshold to determine if thewaveforms 500, 600 are physiologic waveforms. If the slew rate 606 isgreater than the slew rate 506 (or exceeds the slew rate 506 by at leasta predetermined threshold), then the slew rate 606 may be determined at308 to indicate that the corresponding waveform 600 is non-physiologic.Alternatively, if the slew rate 606 exceeds a predetermined slew ratethreshold then the slew rate 606 may be determined at 308 to indicatethat the waveform 600 is non-physiologic.

Amplitudes 508, 608 of the waveforms 500, 600 represent a peak gain orstrength 510, 610 of each waveform 500, 600. As shown in FIG. 5, thewaveform 500 has approximately constant amplitudes 508 during theillustrated time period. While the waveform 600 may have approximatelyconstant amplitudes 608, these amplitudes 608 may correspond to themaximum signal gain capability of the amplifiers 268 and 270. Forexample, the gain of signals sensed over a channel may be amplified byan amplifier such as the integrated bipolar amplifier 270 (shown in FIG.2) or the bipolar amplifier 268 (shown in FIG. 2). However, theamplifiers 268, 270 have maximum capabilities gain that are reached wheninput signals have a substantial difference therebetween. These maximumcapabilities may be referred to as the “rails” of the amplifiers 268,270. If the output cardiac signals reach, or “hit” the rail of theamplifier 268, 270, then at 308, it is determined that the sensedsignals may indicate that the corresponding channel is associated with afractured lead or electrode.

Returning to FIG. 3A, at 308, the process 300 may examine the number ofzero crossings 512, 612 occurring over a predetermined time period as aphysiologic indicator. A zero crossing 512, 612 occurs each time thatthe corresponding waveform 500, 600 crosses over the time axis 502, 602.Alternatively, a zero crossing 512, 612 occurs each time the waveforms500, 600 cross over the baseline (not shown) of the waveforms 500, 600.The baselines of the waveforms 500, 600 shown in FIGS. 5 and 6 arecoextensive with the time axes 502, 602, but may be offset above orbelow the time axes 502, 602. The number or frequency of zero crossings512, 612 may be indicative of the physiologic nature of the waveforms500, 600. For example, the number and frequency of zero crossings 612for the waveform 600 is greater than the number and frequency of zerocrossings 512 for the waveform 500 over the same time period shown inFIGS. 5 and 6. The greater number of zero crossings 612 may bedetermined at 308 to indicate that the cardiac signals sensed over thecorresponding channel may not be representative of cardiac behavior.Additionally, the frequency of zero crossings 612 may indicate that thewaveform 600 is not representative of cardiac behavior and therefore isnon-physiologic. For example, the frequency of zero crossings 612 mayvary considerably relative to the frequency of zero crossings 512. Thevarying frequency of zero crossings 612 may indicate that the waveform600 is not representative of cardiac behavior.

In addition or in another embodiment, the waveforms 500, 600 may becompared at 308 to one or more predetermined physiologic waveformtemplates to determine if the morphology, or shape, of the waveforms500, 600 match or correspond to the waveform templates. The waveforms500, 600 may be compared with the waveform templates to generatecorresponding morphology indicators. If the morphology indicator for thewaveform 500 is greater than the morphology indicator for the waveform600, then the morphology indicators may indicate that the waveform 500is physiologic and the waveform 600 is non-physiologic.

Returning to FIGS. 3A and 4, at 308, the waveforms 430, 436 that aresensed over the bipolar and integrated bipolar channels are found to bephysiologic waveforms based on the analysis of one or more of thephysiologic indicators discussed above (e.g., the cardiac rates, slewrates, amplitudes, morphology, and frequency or number of zerocrossings). While the waveforms 430, 436 are physiologic, they areabnormal because the rate threshold was exceeded at 306. Next, inaccordance with one embodiment, flow moves from 308 to 310. At 310, oneor more stimulation pulses (e.g., pacing, antitachycardia pacing,cardioversion or defibrillation) are applied to the heart 102 (shown inFIG. 1). For example, the waveforms 430, 436 are determined to havesimilar cardiac rates (at 304), to have cardiac rates that exceed apredetermined rate threshold (at 306) and to be physiologic waveforms(at 308), thereby indicating that the waveforms 430, 436 are notillustrative of a potential lead fracture, but do indicate tachycardia.As a result, no alert or notification of a potential lead failure isprovided (as shown in the row 420) and no mitigating action is taken (asshown in the row 422). Because the waveforms 430, 436 indicate anabnormal heart rate such as VT or VF, the stimulation pulse is appliedat 310 as a remedial course of action (as shown in the row 424). Oncethe stimulation pulse is applied, the process 300 may return to 302 tosense additional cardiac signals over the bipolar and integrated bipolarchannels.

Returning to 308 in FIG. 3A, when the signals are determined to bephysiologic, flow may move along an alternative path 309 instead ofgoing directly to 310. When flow moves along 309, the process 300suspends therapy (at least temporarily) until additional analysis can beperformed at 311 to confirm or reject a potential arrhythmia. When anarrhythmia is confirmed at 311, a therapy is delivered. When a potentialarrhythmia is rejected as false or negative, no therapy is delivered,and flow returns to 302.

FIG. 3B illustrates the process performed at 311 to confirm or reject apotential arrhythmia. At 330, the hemodynamic monitor module 267 obtainshemodynamic signals, such as from a memory buffer or from one or more ofsensors 115, 117 and 119. The hemodynamic signals represent a secondaryindicator of heart condition. At 332, the arrhythmia confirmation module269 utilizes the secondary indicators (hemodynamic signals) to confirmor reject that the heart is experiencing an arrhythmia. As noted above,the hemodynamic indicator may represent an impedance plethysmothographymeasurement indicative of stroke volume, a pressure signal from a sensorlocated in a heart chamber, a heart sound signal, or a peak endocardialacceleration signal. The hemodynamic signals may be analyzed relative totemplates or in connection with predetermined thresholds. Optionally,the hemodynamic signals may be analyzed relative to previously acquiredhemodynamic signals from the same patient or a pool of patients. In thepresent example, the hemodynamic signals are obtained from thehemodynamic sensor after the first and/or second signals from the firstand/or second channels are determined to be indicative of a potentiallead failure. Optionally, hemodynamic signals may be continuouslyobtained throughout operation and not necessarily only afterdetermination of a potential lead failure based on the first or secondcardiac signals.

When the hemodynamic signals confirm an arrhythmia at 332, flow moves to342 where a stimulation therapy is applied. When, at 332, thehemodynamic signals do not confirm an arrhythmia, but instead areindicative of normal sinus rhythm, flow moves to 334. When flow reaches334, contradictory indicators have occurred, namely one or both of thefirst and second channels have indicated an arrhythmia, while thehemodynamic secondary indicators have indicated normal sinus rhythm. Inthis situation, it may not be necessary or desirable to immediatelyapply stimulation at 342. Instead, it may be desirable at 334 to, atleast temporarily, suspend therapy delivery. Once the therapy istemporarily suspended, flow moves to 336 at which the hemodynamicmonitor module 267 collects supplemental data (e.g., from memory bufferor from sensors 115, 117 and 119 if needed). Optionally, the operationat 336 may be entirely removed and flow may pass directly to 338 wherethe arrhythmia confirmation module 269 performs additional confirmationanalysis seeking to confirm or reject the arrhythmia.

During the supplemental analysis time at 338, the arrhythmiaconfirmation module 269 performs confirmation analysis, such as byanalyzing prior and/or new cardiac signals. Optionally, the confirmationanalysis may analyze prior and/or new hemodynamic signals. Theconfirmation analysis may utilize more time consuming, robust algorithmsfor detecting arrhythmias that may not be readily usable in real timeand continuously during normal operation of the IMD 100. The additionalarrhythmia detection algorithms may be based solely upon analysis ofpre-existing or new cardiac signals. The arrhythmia detection algorithmsmay be based solely upon pre-existing or new hemodynamic signals, or maybe based on a combination of pre-existing and new cardiac andhemodynamic signals. The confirmation analysis may review cardiac and/orhemodynamic signals from other chambers of the heart (e.g., the leftventricle and left atrium) may collect and analyze new cardiac orhemodynamic signals and the like.

Once the confirmation analysis is complete at 338, it is determined at340 whether the confirmation analysis has verified the arrhythmia orprovided a negative result indicating that an arrhythmia does not exist.When the arrhythmia is verified, flow moves to 342 at which thestimulation therapy is now applied. When, at 340, the confirmationanalysis provides a negative result indicating that no arrhythmia ispresent, flow moves to 344 at which the stimulation therapy is abortedor terminated entirely without being delivered. After 344 and 342, flowmoves to 346 where the process returns to point B at the top of FIG. 3A.

Optionally, the process of FIG. 9 may be implemented (as explainedbelow) in connection with the operations of FIG. 3B. In this alternativeembodiment, the process of FIG. 3B is performed at 911 in FIG. 9 toconfirm or reject a potential arrhythmia. When FIG. 3B is entered fromthe process of FIG. 9, then upon completion of the process in FIG. 3B,flow would return to FIG. 9.

Next, the process 300 will be described in connection with a first typeof lead failure. In FIGS. 4A and 4B, the second column 404 of the table400 represents identification of a first type of lead failure using theprocess 300. The first type of lead failure involves failure of anelectrode that is used in only one of the first and second channels overwhich cardiac signals are sensed. For example, the first type of leadfailure may be associated with the electrode used to sense cardiacsignals on the integrated bipolar channel but not on the bipolarchannel. As shown in rows 410, 412 when failure type 1 occurs, thebipolar channel senses physiologic waveform 438 while the integratedbipolar channel senses non-physiologic waveform 440 that does not have aphysiologic shape. As described below, based at least in part of thesewaveforms 438, 440, the process 300 identifies the lead failure as afirst type of lead failure.

At 302, the waveforms 438, 440 are sensed over the bipolar andintegrated bipolar channels, as described above. At 304, the cardiacrates of the waveforms 438, 440 are compared with one another and arefound to differ from one another. The difference in cardiac rates of thewaveforms 438, 440 indicates that at least one of the cardiac signalsrepresents a potential lead failure.

At 312, once the cardiac rates of the waveforms 438, 440 are found todiffer, the memory addresses, to which the cardiac signals (andhemodynamic signals) are stored, may be temporarily blocked to preventoverwriting with additional new cardiac and hemodynamic signals. Forexample, the memory 236 (shown in FIG. 2) may include a memory bufferthat stores a predetermined time period of cardiac signals recentlyobtained over the channels. Another buffer may store a time period ofhemodynamic signals. The memory may be “frozen” and prevented fromstoring additional cardiac and hemodynamic signals in order to preservethe cardiac signals obtained during the previous predetermined timeperiod. Optionally, the content of the cardiac signal memory buffer maybe moved to another section of memory for longer term storage, therebypermitting the memory buffer to continue to store new cardiac signals.Also, hemodynamic signals in the memory buffer may be moved to longerterm memory when waveforms 438, 440 are found to differ.

At 314, the frozen cardiac signals sensed by the integrated bipolarchannel over the previous predetermined time period are obtained fromthe memory. The frozen cardiac signals sensed using the integratedbipolar channel are represented by the cardiac signal waveform 440. Thewaveform 440 is examined to determine if the waveform 440 is aphysiologic or non-physiologic waveform. As described above, the cardiacsignal waveform 440 may be classified as physiologic or non-physiologicby examining one or more physiologic indicators. The waveform 440 isfound to have a non-physiologic waveform at 314. The non-physiologicshape of the waveform 440 may indicate that a potential lead failure hasoccurred and that the potential lead failure is associated with anelectrode used to obtain the cardiac signals over the integrated bipolarchannel.

Thus, flow moves to 316, where the frozen cardiac signals sensed by thebipolar channel over the previous predetermined time period areanalyzed. The cardiac signals from the bipolar channel are examined todetermine if the associated cardiac signal waveform 438 is a physiologicor non-physiologic waveform. As shown in column 404, the waveform 438 isa physiologic waveform.

Thus, flow moves to 318, where the process 300 declares the potentiallead failure to be the first type of lead failure. If the waveform 438of the bipolar channel is physiologic and the waveform 440 of theintegrated bipolar channel is non-physiologic (as determined at 314),the waveforms 438, 440 may indicate that the potential lead failure isassociated with an electrode that was used to obtain the non-physiologicwaveforms 440, but that was not used to obtain the physiologic waveforms438. In an embodiment where the bipolar channel is sensed using the RVtip electrode 122 and the RV ring electrode 124 and the integratedbipolar channel is sensed using the RV tip electrode 122 and the SVCcoil electrode 128, the non-physiologic shape of the waveform 440 mayindicate that the potential lead failure is caused by or associated withthe SVC coil electrode 128.

As shown in rows 418-420, when a type 1 failure occurs, the process 300may notify an operator of the IMD 100 (shown in FIG. 1) or physician ofthe existence of and the type of failure. For example, the IMD 100 maycommunicate with the external device 240 (shown in FIG. 2) to actuate anaudible, visual and/or tactile alarm. The process also seeks to mitigatethe identified lead failure. To do so, the lead coupled with the failedelectrode may be replaced, as indicated in rows 422, 426. The process300 may continue to apply bipolar pacing through the electrodes used tosense signals over the bipolar channel. The integrated bipolar channelmay be disabled by the channel selection module 264 (shown in FIG. 2) toavoid sensing the erroneous signals using the electrode associated withthe failure. Optionally, the channel selection module 264 may enable anew third channel for sensing that utilizes a different combination ofelectrodes to replace the disabled channel.

Optionally, at 318, it may obtain a secondary indicator from theelectrode associated with the lead failure. For example, the process 300verifies an identified lead failure by examining an electrical impedancecharacteristic of the electrode associated with the lead failure. Oncethe electrode is identified, the impedance measuring circuit 218 (shownin FIG. 2) measures the electrical impedance of the electrode. If theimpedance exceeds a predetermined impedance threshold, then theimpedance may represent a secondary indicator to indicate a fracture inthe electrode. The secondary indication of an electrode fractureverifies the lead failure identified by the process 300.

Next at 319, it is determined whether the cardiac rate of the bipolar(first) channel signals exceeds a predetermined rate threshold. When thecardiac rate is below the rate threshold, then the process 300 may moveto point B at the top of FIG. 3A and restart. When the cardiac rateexceeds the rate threshold, flow may move along path 315 to 311 wheretherapy is suspended until an additional confirmation analysis isperformed to confirm or reject the arrhythmia as described above inconnection with FIG. 3B.

Next, a second type of failure will be described. In FIGS. 4A and 4B,the third column 406 of the table 400 represents identification of asecond type of lead failure using the process 300. Similar to the firsttype of lead failure, the second type involves failure of an electrodethat is used in only one of the two channels over which cardiac signalsare sensed. For example, the second type of lead failure may beassociated with the electrode used to sense cardiac signals on thebipolar channel, but not on the integrated bipolar channel.

At 302, the waveforms 442, 444 are sensed over the bipolar andintegrated bipolar channels, as described above. As shown in rows 410,412, the second type of lead failure may result in the bipolar channelsensing a non-physiologic waveform 442, while the integrated bipolarchannel senses a physiologic waveform 444. As described below, based atleast in part on these sensed waveforms 442, 444, the process 300identifies the lead failure as the second type of lead failure. To doso, at 304, the cardiac rates of the waveforms 442, 444 are comparedwith one another and are found to differ from one another. Thedifference in cardiac rates of the waveforms 442, 444 may indicate thatat least one of the cardiac signals represents a potential lead failure.At 312, the memory is frozen to prevent storage of additional cardiacsignals on the bipolar and integrated bipolar channels, as describedabove. At 314, the integrated bipolar cardiac signals are examined todetermine if the signals (e.g., the waveform 444) indicate a physiologicwaveform. The waveform 444 is found to have a physiologic waveform.

At 320, after the integrated bipolar channel signals are found torepresent a physiologic waveform, the bipolar channel signals areexamined to determine if the waveform 442 is a physiologic waveform.When the first channel signal is physiologic at 320, flow moves alongpath A to 306. When not physiologic at 320, flow moves to 322.

When both of the bipolar channel signals are found to be physiologicwaveforms at 314 and 320, the cardiac rates of one or more of thebipolar channel signals and the integrated bipolar channels may becompared to a predetermined cardiac rate threshold at 306, as describedabove. If the cardiac rates are sufficiently high at 306, the process300 may proceed through 308 to 310 where the stimulation pulse isapplied. Otherwise, the process 300 may proceed back to 302.

Returning to 320, when the first channel is not physiologic, then at322, the process 300 declares the lead failure to be the second type oflead failure. For example, as the bipolar channel signals represent anon-physiologic waveform while the integrated bipolar channel signalsrepresent a physiologic waveform, the process 300 determines that anelectrode used to obtain the bipolar channel signals but not to obtainthe integrated bipolar channel signals is associated with the leadfailure. In an embodiment where the bipolar channel obtains signalsusing the RV tip electrode 122 (shown in FIG. 1) and the RV ringelectrode 124 (shown in FIG. 1) and the integrated bipolar channelobtains signals using the RV tip electrode 122 and the SVC coilelectrode 128 (shown in FIG. 1), the process 300 declares the leadfailure to be associated with the RV ring electrode 124. The process 300may verify the second type of lead failure by measuring, at 322, asecondary electrode indicator such as an electrical impedancecharacteristic of the associated electrode, as described above.

As shown in rows 418-428 of FIGS. 4A and 4B, the process 300 at 322 maynotify an operator of the IMD 100 (shown in FIG. 1) or a physician ofthe existence and type of the failure. The IMD 100 may mitigate thesecond type of lead failure by continuing to operate while ignoring thesignals obtained by the electrodes associated with the bipolar channel.For example, the IMD 100 may disable sensing over the bipolar channel.The process 300 may remedy the lead failure at least in part bydirecting the IMD 100 to switch from bipolar pacing to integratedbipolar pacing of the heart 102 (shown in FIG. 1). For example, theprocess 300 may direct the IMD 100 to refrain from using the RV tipelectrode 122 and RV ring electrode 124 to pace the heart 102 andinstead use the RV tip electrode 122 and the SVC coil electrode 128 topace the heart 102.

After 322, it is determined at 323 whether the signal over the secondchannel has a rate that exceeds a rate threshold. If not, flow returnsto the start at B. If the second channel has a signal rate that exceedsthe rate threshold, flow moves to 311 where therapy is suspended atleast temporarily as discussed above.

Next, the third type of failure is discussed. In FIGS. 4A and 4B, thefourth column 408 of the table 400 represents identification of a thirdtype of lead failure using the process 300. In contrast to the first andsecond types of lead failure, the third type involves the failingelectrode and is common to two or more of the channels over whichcardiac signals are sensed. For example, the third type of lead failuremay be associated with the electrode used to sense cardiac signals onthe bipolar and integrated bipolar channels.

At 302, the waveforms 446, 448 are sensed over the bipolar andintegrated bipolar channels, as described above. As shown in the rows410, 412, both the bipolar and integrated bipolar channels sensenon-physiologic waveforms 446, 448. At 304, the cardiac rates of thewaveforms 446, 448 are compared with one another and are found to differfrom one another. The difference in rates of the waveforms 446, 448 mayindicate that at least one of the cardiac signals represents a potentiallead failure. At 312, the memory is frozen and prevented from storingadditional hemodynamic and cardiac signals. At 314, the integratedbipolar cardiac signals are examined to determine if the signals (e.g.,the waveform 448) represent a physiologic waveform. In the embodimentrepresented by the column 408, the waveform 448 is found to have anon-physiologic waveform. At 316, after the integrated bipolar channelsignals are found to be non-physiologic (at 314); the bipolar channelsignals are examined to determine if the signals (e.g., the waveform446) are physiologic. In the embodiment represented by the column 408,the waveform 446 is found to have a non-physiologic waveform.

At 324, after the bipolar and integrated bipolar channel signals aredetermined to be non-physiologic at 314 and 316, the bipolar andintegrated bipolar channel signals are compared to determine if thesignals are correlated with one another. For example, the signals may becompared to determine if the signals approximately match one anotherover a predetermined time period. One or more of the physiologicindicators described above may be used to determine if the bipolar andintegrated bipolar channel signals are correlated with one another. Ifat least a predetermined number of the physiologic indicators for eachof the bipolar and integrated bipolar channels are within apredetermined range or variance of one another, then the bipolar andintegrated bipolar channel signals may be correlated with one another.In the embodiment shown in the fourth column 408, the bipolar andintegrated bipolar channel signals shown in the rows 410, 412 are foundto be correlated with one another.

At 324, when the signals from the bipolar and integrated bipolarchannels are not correlated with one another, the signals may notindicate that the potential lead failure is the third type of leadfailure. Instead, the signals may indicate a different type of leadfailure or that no lead failure has occurred. As a result, the process300 may return to 302 where additional signals are obtained over thechannels to determine if a potential lead failure exists or if the IMD100 (shown in FIG. 1) is operating in the “no fault” category describedin column 402 of the table 400 and described above.

At 324, when the bipolar and integrated bipolar channel signals arefound to be correlated with one another, at 326, the process 300identifies the potential lead failure as the third type of failure. Forexample, when both of the bipolar and integrated bipolar signals arefound to be non-physiologic and correlated with one another, theelectrode that is common to both the bipolar and integrated bipolarchannels is identified as associated with the lead failure. In anembodiment where the RV tip electrode 122 (shown in FIG. 1) is used tosense cardiac signals on both the bipolar and integrated bipolarchannels, the RV tip electrode 122 is associated with the lead failure.The process 300 may verify the lead failure by measuring an electricalimpedance characteristic of the associated electrode, as describedabove.

An operator or physician may be notified of the existence and type ofthird type of lead failure. As shown in row 422 of the table 400, thethird type of lead failure may be mitigated by disabling the channelsassociated with the failed electrode. For example, the IMD 100 (shown inFIG. 1) may ignore cardiac signals obtained over both the bipolar andintegrated bipolar channels. As the electrode associated with the leadfailure is used to obtain signals over both channels, the signalsobtained over both channels are affected by the failed electrode. Inorder to avoid pacing or applying stimulation pulses based on signalsobtained over a failed lead, both channels are ignored. The IMD 100 mayavoid pacing the heart 102 (shown in FIG. 1) or applying stimulationpulses to the heart 102, even if the cardiac rates of the signalsobtained over the channels indicate a sufficiently high rate such that astimulation pulse would otherwise be applied. As shown in row 426, thelead 104-108 (shown in FIG. 1) having the electrode associated with thelead failure may be replaced in order to remedy the lead failure.Alternatively, the IMD 100 may be reconfigured to use differentcombinations of electrodes to sense cardiac signals over a differentchannel. For example, if the RV tip electrode 122 (shown in FIG. 1) isdeclared to be the electrode associated with the lead failure, the IMD100 may switch to sensing cardiac signals over a third channel differentfrom the bipolar and integrated bipolar channels. The third channel maybe sensed using the RV ring electrode 124 (shown in FIG. 1) and the SVCcoil electrode 128 (shown in FIG. 1), or another combination ofelectrodes coupled with the failed lead or with another lead.

After 326, flow moves to 311, where hemodynamic signals are collectedand analyzed to confirm or reject arrhythmias as discussed in connectionwith FIG. 3B.

In one embodiment, the third type of lead failure may be detected by theprocess 300 in a different manner. As described above in connection withthe “no fault” operation of the IMD 100 (shown in FIG. 1), at 308, thesignals obtained over the bipolar and integrated bipolar channels areexamined to determine if the signals have physiologic waveforms. If thewaveforms do not have physiologic waveforms, the signals may indicatethe third type of lead failure. For example, while the signals may havesimilar cardiac rates (determined at 304) and the cardiac rates exceed arate threshold (determined at 306), the signals on both channels may bebased on a lead failure involving an electrode common to both channels.In order to check for the third type of lead failure, at 324, thesignals are compared to determine if the signals are correlated asdescribed above. Based on this additional check, the process 300 maydeclare that the signals are based on the third type of lead failure.For example, the third type of lead failure may be identified when boththe bipolar and integrated bipolar channel signals are non-physiologicand correlated with one another

FIG. 7 illustrates a block diagram of exemplary manners in whichembodiments of the present invention may be stored, distributed, andinstalled on a computer-readable medium. In FIG. 7, the “application”represents one or more of the methods and process operations discussedabove. The application is initially generated and stored as source code700 on a source computer-readable medium 702. The source code 700 isthen conveyed over path 704 and processed by a compiler 706 to produceobject code 708. The object code 708 is conveyed over path 710 and savedas one or more application masters on a master computer-readable medium712. The object code 708 is then copied numerous times, as denoted bypath 714, to produce production application copies 716 that are saved onseparate production computer-readable medium 718. The productioncomputer-readable medium 718 is then conveyed, as denoted by path 720,to various systems, devices, terminals and the like. A user terminal722, a device 724 and a system 726 are shown as examples of hardwarecomponents, on which the production computer-readable medium 718 areinstalled as applications (as denoted by 728 through 732). For example,the production computer-readable medium 718 may be installed on the IMD100 (shown in FIG. 1) and/or the microcontroller 216 (shown in FIG. 2).Examples of the source, master, and production computer-readable medium702, 712, and 718 include, but are not limited to, CDROM, RAM, ROM,Flash memory, RAID drives, memory on a computer system, and the like.Examples of the paths 704, 710, 714, and 720 include, but are notlimited to, network paths, the internet, Bluetooth, GSM, infraredwireless LANs, HIPERLAN, 3G, satellite, and the like. The paths 704,710, 714, and 720 may also represent public or private carrier servicesthat transport one or more physical copies of the source, master, orproduction computer-readable medium 702, 712 or 718 between twogeographic locations. The paths 704, 710, 714 and 720 may representthreads carried out by one or more processors in parallel. For example,one computer may hold the source code 700, compiler 706 and object code708. Multiple computers may operate in parallel to produce theproduction application copies 716. The paths 704, 710, 714, and 720 maybe intra-state, inter-state, intra-country, inter-country,intra-continental, inter-continental, and the like.

The operations noted in FIG. 7 may be performed in a widely distributedmanner world-wide with only a portion thereof being performed in theUnited States. For example, the application source code 700 may bewritten in the United States and saved on a source computer-readablemedium 702 in the United States, but transported to another country(corresponding to path 704) before compiling, copying and installation.Alternatively, the application source code 700 may be written in oroutside of the United States, compiled at a compiler 706 located in theUnited States and saved on a master computer-readable medium 712 in theUnited States, but the object code 708 transported to another country(corresponding to path 714) before copying and installation.Alternatively, the application source code 700 and object code 708 maybe produced in or outside of the United States, but productionapplication copies 716 produced in or conveyed to the United States (forexample, as part of a staging operation) before the productionapplication copies 716 are installed on user terminals 722, devices 724,and/or systems 726 located in or outside the United States asapplications 728 through 732. As used throughout the specification andclaims, the phrases “computer-readable medium” and “instructionsconfigured to” shall refer to any one or all of (i) the sourcecomputer-readable medium 702 and source code 700, (ii) the mastercomputer-readable medium and object code 708, (iii) the productioncomputer-readable medium 718 and production application copies 716and/or (iv) the applications 728 through 732 saved in memory in theterminal 722, device 724, and system 726.

FIG. 8 illustrates a sensor subsystem 800 formed in accordance with analternative embodiment. The sensor subsystem 800 may be used in place ofthe sensing amplifiers 268 and 270 in FIG. 2. The sensor subsystem 800includes an SVC far-field bipolar sensing amplifier (SBSA) 802, anintegrated bipolar sensing amplifier (IBSA) 806 and a bipolar sensingamplifier (BSA) 804. The SBSA 802, BSA 804 and IBSA 806 each include apair of input lines that may be joined to various combinations ofelectrodes based on the configuration of the switch 232 (FIG. 2). In theexample of FIG. 8, the SBSA 802 is joined to an SVC shocking coilelectrode and an active fixation helix electrode (RV tip) of the lead.The IBSA 806 is joined to an RV shocking coil electrode and the tipelectrode. The BSA 804 is joined to the RV ring electrode and the tipelectrode. While in the example of FIG. 8, the SBSA 802, BSA 804 andIBSA 806 are each joined to the tip electrode, it is understood that theSBSA 802, BSA 804 and IBSA 806 may be joined to a common differentelectrode, or alternatively joined to separate pairs of electrodes.

As explained above, the potential exists for various types of failuresto occur. The inputs to the SBSA 802, BSA 804 and IBSA 806 have beenlabeled with potential “failures” that are described in connection withFIGS. 9-12. The SBSA 802, BSA 804 and IBSA 806 define sensing channels.For example, the BSA 804 and IBSA 806 define first and second sensingchannels as discussed above in connection with FIGS. 1-7. The SBSA 802defines a third sensing channel that outputs a difference signal betweenthe SVC shocking coil electrode and the tip electrode. The SBSA 802, BSA804 and ISBA 806 provide respective difference output signals to the A/Dconverter 230.

FIG. 9 illustrates a process 900 for detecting potential lead or channelfailures of the IMD 100 (shown in FIG. 1) with the sensing subsystem 800shown in FIG. 8. The process 900 represents a lead failure detectionscheme for implanted leads, where the process 900 utilizes simultaneousor sequential sensing of at least three signals to detect shorts betweenconductors or open circuits. The lead or channel failures may arise inconnection with temporary or permanent failure of the electricalconduction path (e.g., a break or fracture in the conductive wirecreating an open circuit) associated with a single electrode, such asany one of the SVC shocking coil, RA electrode, RV shocking coil, RVring, RV tip active fixation helix, LA coil electrode, LA ringelectrode, LV coil electrode, LV ring electrode, LV tip electrode andthe like. When a conductive path fails in connection with a singleelectrode by forming an open or closed circuit, then the differentialsignals created based on the particular electrode are affected.

The operations of FIGS. 9 and 12, and the conditions in FIGS. 10A and10B and 11A and 11B are primarily discussed in connection collection ofsignals over three separate channels such as defined by the circuits inFIGS. 8 and 13. Optionally, FIGS. 9-12 may be implemented with fewerthan three channels, where one channel sensing multiple signals atdifferent points in time.

For example, the first and second signals may be sensed over a commonchannel associated with the BSA 804, yet collected at successive pointsin time T1 and T2. The third signal may be sensed over a channelassociated with the ISBA 806 or SBSA 802. Alternatively, the ISBA 806 orSBSA 802 may be used to collect two of the three signals, while anotherone of the BSA 804, ISBA 806 and SBSA 802 collect one signal. In thisalternative embodiment, the rows 1010-1013 would correspond to thesignals sensed, and not necessarily three different channels.

As a further option, the processes of FIGS. 9-12 may be implementedutilizing with a sensor subsystem that has more or fewer than threechannels. For example, FIGS. 9-12 may be utilized to analyze conditionsof the sensor subsystem in FIG. 2 which uses two channels defined by aBSA 268 and IBSA 270. For example, BSA 268 may be used to collect firstand second signals, while IBSA 270 may be used to collect a thirdsignal.

The operations performed in FIG. 9 at 902 to 926 are the same as theoperations performed in FIG. 3 at 302 to 326, respectively. Therefore,the operations at 902-926 are described in a summary manner. The process900 operates to determine if a channel failure has occurred and, if achannel failure has occurred, to identify the electrode(s) associatedwith the failure. The process 900 may continue to operate, after achannel failure, is identified to determine if any additional channelfailures occur.

FIGS. 10A and 10B illustrate a table 1000, similar to the Table in FIGS.4A and 4B, but with an additional row 1013 and an additional column1005. The content of rows 1010, 1012, and 1014-1028 are the same as thecontent of rows 410 to 428 in FIGS. 4A and 4B. Optionally, when morethan one signal is obtained from one channel, then the rows 1010-1013represent different signals, one or more of which may be collected froma common channel at different points in time. The content of columns1002, 1004, 1006 and 1008 are the same as the content of columns 402,404, 406 and 408, respectively. Each column 1002-1008 includesinformation and data relevant to different types of lead or channelstates. Each column 1004-408 corresponds to a different type or categoryof lead or channel state, such as no fault, failure type 1, etc. Column1005 corresponds to Failure type 4, discussed below in more detail, andrelated to an open circuit or chatter failure of the third channelassociated with one input to the SBSA 802. The information in FIGS. 10Aand 10B will be referenced in connection with the following discussionof the process 900 in FIG. 9.

At 902, during the “no fault” operation of the lead 94 (shown in FIG.1), cardiac signals are simultaneously sensed over multiple channels,such as the bipolar (or first) channel, the integrated bipolar (orsecond) channel and the SVC far-field bipolar (or third) channel. Thefirst column 1002 of the table 1000 is associated with application ofthe process 900 when detecting a “no fault” condition of the IMD 100.The cell at the intersection of the first row 1010 and the first column1002 illustrates an example of a normal physiologic bipolar waveform1030. The cell at the intersection of the second row 1012 and the firstcolumn 1002 illustrates an example of a second or integrated bipolarwaveform 1036 that is sensed over the integrated bipolar channel duringthe “no fault” state of the lead 94. The cell at the intersection of thethird row 1013 and the first column 1002 illustrates an example of athird or SVC far-field bipolar waveform 1037 that is sensed over the SVCfar-field bipolar channel during the “no fault” state of the lead 94.

In FIG. 9, at 904, the three cardiac signals sensed (e.g., from two orthree of the SVC, bipolar and integrated bipolar channels) are comparedto one another. If the cardiac rates are found to be similar at 904, thecardiac rates sensed over the SVC far-field bipolar, bipolar andintegrated bipolar channels are compared at 906 to a predetermined ratethreshold. If the cardiac rates exceed the rate threshold, then thecardiac rates may be indicative of an abnormal heart rate.Alternatively, if the cardiac rates do not exceed the rate threshold orare not otherwise indicative of an abnormal heart rate, then the process900 returns to 902. If the cardiac rates are found to exceed the ratethreshold at 906, flow moves to 908 where the cardiac signals areexamined to determine if the signals correspond to physiologic (normalor abnormal) cardiac waveforms. For example, as shown in FIG. 10A at thecell at the intersection of row 1016 and column 1002, when asimultaneous or concurrent high rate is found in two cardiac signals(e.g., sensed over the bipolar and integrated bipolar channels), aphysiologic test may be performed on the cardiac signals.

In one embodiment, the physiologic test at 908 involves analyzing valuesof one or more physiologic indicators or parameters of the cardiacsignals sensed over the SVC far-field bipolar, bipolar and integratedbipolar channels. The physiologic indicators may include the cardiacrates, a slew rate, a zero crossing rate, and an amplitude of thecardiac signal waveforms.

At 908, the waveforms 1030, 1036, 1037 are found to be physiologicwaveforms based on the analysis of one or more of the physiologicindicators discussed above (e.g., the cardiac rates, slew rates,amplitudes, morphology, and frequency or number of zero crossings).While the waveforms 1030, 1036 1037 are physiologic, in the presentexamples, they are abnormal because the rate threshold was exceeded at906. Next, at 910, one or more stimulation pulses are applied to theheart 102 (shown in FIG. 1). Once the stimulation pulse is applied, theprocess 900 may return to 902 to sense additional cardiac signals overthe SVC far-field bipolar, bipolar and integrated bipolar channels.

Returning to 908 in FIG. 9, when the signals are determined to bephysiologic, but abnormal flow may move along an alternative path 909instead of going directly to 910. When flow moves along 909, the process900 suspends therapy (at least temporarily) until additional analysiscan be performed at 911 to confirm or reject a potential arrhythmia.When an arrhythmia is confirmed at 911, a therapy is delivered. When apotential arrhythmia is rejected as false or negative, no therapy isdelivered, and flow returns to 902. FIG. 3B illustrates the processperformed at 911 to confirm or reject a potential arrhythmia.

Next, the process 900 will be described in connection with a first typeof lead failure. The first type of lead failure involves failure of anelectrode that is used in only one of the channels over which cardiacsignals are sensed. As shown in rows 1010, 1012, 1013 when failure type1 occurs, the bipolar channel senses physiologic waveform 1038, the SVCfar-field bipolar channel senses physiologic waveform 1039, while theintegrated bipolar channel senses non-physiologic waveform 1040 thatdoes not have a physiologic shape. As described below, based at least inpart on these waveforms 1038, 1039, 1040, the process 900 identifies thelead failure as a first type of lead failure.

At 904, once the cardiac rates of the waveforms 1038, 1039, 1040 arefound to differ, flow moves to 912 where the memory addresses, to whichthe cardiac signals (and hemodynamic signals) are stored, may betemporarily blocked to prevent overwriting with additional new cardiacand hemodynamic signals. At 912, the frozen cardiac signals sensed bythe SVC far-field, bipolar, and integrated bipolar channels are obtainedfrom the memory.

When the rates are found to be dissimilar at 904, flow branches alongtwo parallel paths. One path is shown in FIG. 9 at 912 to 956, and isused to detect and manage closed or open circuit states associated witha single electrode. The other path is shown in FIG. 12, and is used todetect and manage closed or short circuit states associated with two ormore electrodes. Optionally, the process of FIG. 12 may be performedserially before or after the operations at 912-956.

At 914, the waveform 1040 is examined to determine if the waveform 1040is a physiologic or non-physiologic waveform. The waveform 1040 is foundto have a non-physiologic waveform at 914. Thus, flow moves to 916,where the cardiac signals from the bipolar channel are examined todetermine if the associated cardiac signal waveform 1038 is aphysiologic or non-physiologic waveform. As shown in column 1004, thewaveform 1038 is a physiologic waveform.

Thus, flow moves to 918, where the process 900 declares the potentiallead failure to be the type 1 lead failure. If the waveform 1038 of thebipolar channel is physiologic and the waveform 1040 of the integratedbipolar channel is non-physiologic (as determined at 914), the waveforms1038, 1040 may indicate that the potential lead failure is associatedwith an electrode that was used to obtain the non-physiologic waveforms1040, but that was not used to obtain the physiologic waveforms 1038.

Optionally, at 916, the waveform 1039 sensed over the SVC far-fieldbipolar or third channel may also be analyzed instead of, or in additionto, the waveform 1038 sensed over the bipolar or first channel, todetermine whether the waveform 1039 is physiologic. If the waveform 1039sensed over the SVC far-field bipolar channel is not physiologic, thismay be an indicator of a type 3 failure, as explained below.

As shown in rows 1018-1020, when a type 1 failure occurs, the process900 may notify an operator of the IMD 100 (shown in FIG. 1) or physicianof the existence and type of failure. The process also seeks to mitigatethe identified lead failure. The process 900 may continue to applybipolar pacing through the electrodes used to sense signals over thebipolar channel. The faulty electrode may be disabled by the channelselection module 264 (shown in FIG. 2) to avoid sensing the erroneoussignals using the electrode associated with the failure. Optionally, thechannel selection module 264 may enable a new channel for sensing thatutilizes a different combination of electrodes to replace the disabledelectrode.

Next at 919, it is determined whether the cardiac rate of the firstand/or third signals, exceed a predetermined rate threshold. When thecardiac rate is below the rate threshold, then the process 900 may moveto point B at the top of FIG. 9 and restart. When the cardiac rateexceeds the rate threshold, flow may move along path 915.

Next, a type 2 failure will be described. In FIGS. 10A and 10B, thecolumn 1006 of the table 1000 represents an identification of a secondtype of lead failure using the process 900. At 902, the waveforms 1042,1044, 1047 are sensed. As shown in rows 1010, 1012, 1013 the second typeof lead failure may result in the bipolar channel sensing anon-physiologic waveform 1042, while the integrated bipolar channelsenses a physiologic waveform 1044 and the SVC far-field bipolar channelsenses a physiologic waveform 1047. As described below, based at leastin part on these sensed waveforms 1042, 1044, 1047 the process 900identifies the lead failure as the second type of lead failure. To doso, at 904, the cardiac rates of the waveforms 1042, 1044 are comparedwith one another and are found to differ from one another. Thedifference in cardiac rates of the waveforms 1042, 1044, 1047 mayindicate that at least one of the cardiac signals represents a potentiallead failure. At 912, the memory is frozen, and at 914, the integratedbipolar cardiac signals are examined to determine if the signals (e.g.,the waveform 1044) indicate a physiologic waveform. The waveform 1044 isfound to have a physiologic waveform.

At 920, the first or bipolar channel signals are examined to determineif the waveform 1042 is a physiologic waveform. When the first channelsignal is physiologic at 920, flow moves to 952. When not physiologic at920, flow moves to 922. At 922, the process 900 declares the leadfailure to be the type 2 lead failure.

As shown in rows 1018-1028 of FIG. 10B, the process 900 at 922 maynotify an operator of the IMD 100 (shown in FIG. 1) or a physician ofthe existence and type of the failure. The IMD 100 may mitigate thesecond type of lead failure by continuing to operate while ignoring thesignals obtained by the electrodes associated with the bipolar channel.For example, the IMD 100 may disable sensing over the bipolar channel.The process 900 may remedy the lead failure at least in part bydirecting the IMD 100 to switch from bipolar pacing to integratedbipolar pacing of the heart 102 (shown in FIG. 1).

After 922, it is determined at 923 whether the second and/or thirdsignals have a rate that exceeds a rate threshold. If not, flow returnsto the start at B. If the second and/or third channel has a signal ratethat exceeds the rate threshold, flow moves to 911 where therapy issuspended at least temporarily pending confirmation as discussed above.

Next, the type 3 failure is discussed. In FIGS. 10A and 10B, the column1008 of the table 1000 represents identification of a type 3 leadfailure using the process 900. In contrast to the first and second typesof lead failure, the third type involves a failing electrode that iscommon to two or more of the channels over which cardiac signals aresensed. For example, the third type of lead failure may be associatedwith the tip electrode used to sense cardiac signals on the bipolar,integrated bipolar and SVC far-field bipolar channels. Optionally, thethird type may be associated with a different electrode common to two ormore channels.

At 902, the waveforms 1046, 1048, 1049 are sensed. As shown in the rows1010, 1012, 1013, the SVC far-field bipolar, bipolar and integratedbipolar channels all sense non-physiologic waveforms 1046, 1048, 1049.At 904, the cardiac rates of the waveforms 1046, 1048, 1049 are comparedwith one another and are found to differ from one another. The flowsplits in parallel between FIG. 12 and to 912 in FIG. 9. At 912, thememory is frozen and prevented from storing additional hemodynamic andcardiac signals. At 914, the integrated bipolar cardiac signals areexamined to determine if the signals (e.g., the waveform 1048) representa physiologic waveform. At 916, after the integrated bipolar channelsignals are found to be non-physiologic (at 914), the bipolar channelsignals are examined to determine if the signals (e.g., the waveform1046) are physiologic.

At 924, the first and second signals are compared to determine if thesignals are correlated with one another. Various types of correlationanalysis may be performed. For example, the signals may be compared todetermine similarity in the positive and/or negative portions of thesignals. Optionally, the correlation may represent a comparison of anumber of peaks (+/−), amplitude (+/−), slope changes, slew rates, rate,and the like. At 924, when the signals from the bipolar and integratedbipolar channels are not correlated with one another, the signals maynot indicate that the potential lead failure is the third type of leadfailure. Instead, the signals may indicate a different type of leadfailure or that no lead failure has occurred. As a result, the process900 may return to 902 where additional signals are obtained over thechannels to determine if a potential lead failure exists or if the IMD100 (shown in FIG. 1) is operating in the “no fault” category describedin column 1002 of the table 1000 and described above.

At 924, when the bipolar and integrated bipolar channel signals arefound to correlate with one another, flow moves to 912. At 926, theprocess 900 identifies the potential lead failure as the third type offailure. An operator or physician may be notified of the existence andtype of the lead failure. As shown in row 1022 of the table 1000, thethird type of lead failure may be mitigated by disabling the channelsassociated with the failed electrode. In order to avoid pacing orapplying stimulation pulses based on signals obtained over a failedlead, both channels are ignored. Alternatively, the IMD 100 may bereconfigured to use different combinations of electrodes to sensecardiac signals over a different channel. After 926, flow moves to 911,where hemodynamic signals are collected and analyzed to confirm orreject arrhythmias.

Next, a type 4 failure is discussed. In FIGS. 10A and 10B, the column1005 of the table 1000 represents identification of a fourth type oflead or channel failure using the process 900. In contrast to the leadfailure types 1-3, the fourth type may involve failure of the SVCshocking coil electrode or other far-field sensing electrode which isnot common to the other channels over which cardiac signals are sensed.For example, the fourth type of lead or channel failure may beassociated with the electrode used to sense cardiac signals only overthe SVC far-field bipolar channel.

At 902, the waveforms 1043, 1041, 1045 are sensed. As shown in the rows1010, 1012, 1013, only the SVC far-field bipolar channel senses anon-physiologic waveform 1045, while the bipolar and integrated bipolarchannels sense physiologic waveforms 1043, 1041. At 904, the cardiacrates of the waveforms 1043, 1041, 1045 are compared with one anotherand are found to differ from one another. Parallel flow moves to FIG.12. At 912, the memory is frozen and prevented from storing additionalhemodynamic and cardiac signals over the present waveforms of interest.At 914, the integrated bipolar cardiac signals are examined to determineif the signals (e.g., the waveform 1041) represent a physiologicwaveform. At 920, after the integrated bipolar channel signals are foundto be physiologic (at 914), the bipolar channel signals are examined todetermine if the signals (e.g., the waveform 1043) are physiologic.Given that the waveform 1043 (second channel signal) is physiologic,flow moves to 952.

At 952, the cardiac signals sensed over the third (SVC far-fieldbipolar) channel are examined to determine if the signals (e.g., thewaveform 1045) represent a physiologic waveform. When the cardiacsignals sensed over the SVC far-field bipolar channel are found to bephysiologic (at 952), flow skips to point A (at 906). At 906, the methoddetermines whether the three cardiac signals (e.g., sensed over one ormore of the first, second and third channels) exhibit a rate thatexceeds an associated one or more thresholds.

At 952, when the cardiac signals sensed over the SVC far-field bipolarchannel are found to be non-physiologic (as is waveform 1045), flowmoves to 954. At 954, the process 900 declares the potential lead orchannel failure to be the fourth type of lead or channel failure. Giventhat the waveform 1043 of the bipolar channel is physiologic and thewaveform 1041 of the integrated bipolar channel is physiologic, thewaveform 1045 indicates that the potential lead or channel failure isassociated with an electrode that was is unique to the third channel,but that was not used to obtain the physiologic waveforms 1041 or 1043.In the present example, the unique electrode represents the SVC shockingcoil electrode. Alternatively, the electrode unique to the third channelmay be a different electrode, such as an LA electrode, and RA electrodeand LV electrode and the like.

As shown in row 1014, the result of the comparisons at 914, 920 and 952is to determine that the channels sense different rates that are notcorrelated. As shown at row 1016, optionally at 952, the method mayperform a secondary test of the cardiac signals sensed over the thirdchannel. For example, the method may analyze the rate, slew rate,amplitude or another characteristic of the cardiac signals sensed overthe third channel for physiologic behavior.

As shown in rows 1018-1020, when a type 4 failure occurs, the process900 may notify an operator of the IMD 100 (shown in FIG. 1) or physicianof the existence of and the type of failure. For example, the IMD 100may communicate with the external device 240 (shown in FIG. 2) toactuate an audible, visual and/or tactile alarm. The process also seeksto mitigate the identified lead failure. To do so, the failed electrodemay be switched off or replaced with another electrode. For example, theSVC shocking coil may be switched off and replaced with the RAelectrode. The process 900 may continue to apply pacing through theelectrodes used to sense signals over the bipolar and integrated bipolarchannels. The third channel may be disabled by the channel selectionmodule 264 (shown in FIG. 2) to avoid sensing the erroneous signalsusing the electrode associated with the failure. Optionally, the channelselection module 264 may enable a new channel for sensing that utilizesa different combination of electrodes to replace the disabled channel.

As shown at rows 1024 and 1028, once the third channel has been switchedto a new electrode or switched off, the IMD 100 may still provide pacingand shocking stimulus over the bipolar (first) channel when the bipolar(first) channel exhibits an associated rate that warrants therapy.

Optionally, at 954, the method may obtain a secondary indicator from theelectrode associated with the lead or channel failure. For example, theprocess 900 may verify an identified lead failure by examining anelectrical impedance characteristic of the electrode associated with thefailure. Once the electrode is identified, the impedance measuringcircuit 218 (shown in FIG. 2) measures the electrical impedance of theelectrode. If the impedance exceeds a predetermined impedance threshold,then the impedance may represent a secondary indicator to indicate afracture in the electrode. The secondary indication of an electrodefracture verifies the lead failure identified by the process 900.

Next at 956, the method determines whether the cardiac rate of thebipolar and/or integrated bipolar (first and second) channel signalsexceed a predetermined rate threshold. When the cardiac rate is belowthe rate threshold, then the process 900 may move to point B at the topof FIG. 9 and restart. When the cardiac rate exceeds the rate threshold,flow may move along path 915 to 911 where therapy is suspended until anadditional confirmation analysis is performed to confirm or reject thearrhythmia as described above in connection with FIG. 3B.

Optionally, the order of the decisions at 914, 916, 920, 924 and 952 maybe varied. For example the first, second or third signals may beanalyzed at 914, followed by another of these signals. The operations at918, 922, 926 and 954 would be adjusted accordingly.

Next, the discussion turns to conditions in which failures result inclose circuit states between two or more electrodes.

FIGS. 11A and 11B include a table displaying information and datarelevant to various types of closed circuit lead or channel failuresidentified by the process shown in FIG. 12. The content of columns1102-1106 represents information and data relevant to different types oflead or channel states when two or more electrodes (or conductive paths)short with one another. Column 1102 corresponds to no fault. Column 1103corresponds to the situation in which an electrode associated with theintegrated bipolar channel (second channel) short circuits to anelectrode associated with the SVC far-field bipolar channel (thirdchannel), referred to as short circuit failure types 1 and 4. Column1104 corresponds to the situation in which an electrode associated withthe bipolar channel (first channel) shorts to an electrode associatedwith the integrated bipolar channel (second channel), referred to asshort circuit failure types 1 and 2 or (1 and 3). Column 1106corresponds to the situation in which an electrode associated with thebipolar channel (first channel) shorts to an electrode associated withthe SVC far-field bipolar channel (third channel), referred to as shortchatter failure types 4 and 2 or (4 and 3).

The rows 1112-1114 represent examples of the differential waveformsgenerated by the corresponding first, second and third channels. Forexample, waveforms 1141-1143 represent-physiologic waveforms generatedwhen no faults occur. Waveform 1144 is physiologic, while waveforms1145-1146 represent non-physiologic waveforms generated when a shortcircuit occurs in connection with failure types 1 and 4. Waveforms 1147and 1148 are non-physiologic, while waveform 1149 is physiologic, when ashort circuit occurs in connection with failure types 1 and 2, orfailure types 1 and 3. Waveforms 1150 and 1152 are non-physiologic,while waveform 1151 is physiologic, when a short circuit occurs inconnection with failure types 4 and 2, or failure types 4 and 3.

The row 1116 illustrates the results that are determined based on thecombination of failure types that are declared. The row 1118 illustratesadditional/secondary tests that may be performed to determine if signalsare physiologic. The rows 1120-1124 indicate the types of failures thatare declared (row 1120), the clinical alerts that are given (row 1122)and any mitigation that may be performed (row 1124) based on the resultsdetermined in row 1116. The row 1126 indicates the course of action tobe taken when the no-fault channel (e.g., the bipolar channel in column1103, the SVC far-field bipolar channel in column 1104 and theintegrated bipolar channel in column 1106) indicates a physiologicwaveform that has an unduly high rate.

The row 1128 indicates the clinical response to be taken based on thefailure types declared, while the row 1130 indicates whether to continuepacing based on the failure types declared. Next, the cells within thetable of FIGS. 11A and 11B are discussed in connection with each ofcolumns 1103-1106.

Column 1103 corresponds to the condition in which two conductive pathshave shorted together, thereby creating “chatter” in the signals sensedby the corresponding two electrodes (e.g., the SVC shocking coil and theRV shocking coil). When the method of FIG. 12 determines that a shortedcondition has occurred between the SVC shocking coil and the RV shockingcoil, the method determines the result in the cell 1160. Cell 1160indicates that, when a short between two conductive paths causes thetype 1 and type 4 failures, then the method will determine that thefirst (bipolar) channel detects a different rate than the second(integrated bipolar) and third (SVC far-field bipolar). The cell 1160also indicates that signals from the second and the third channelscorrelate with one another. Cell 1164 indicates that more testing may beperformed.

Cell 1168 indicates that the method would declare the conductive pathsthat are associated with the failure types 1 and 4, to be shortedtogether. Cell 1172 indicates that the method would provide a clinicalalert that a potential total system failure is occurring. Cell 1176indicates that the mitigation to occur could be replacement of the lead.Cell 1179 indicates that, if the bipolar channel exhibits a high rate,the IMD 100 should provide a shocking stimulus as the shock may bedelivered regardless of the short between conductive paths.

Cell 1182 indicates that the clinical response should be to replace thelead, while cell 1186 indicates that the IMD 100 should continue to pacethrough the electrodes connected to the bipolar channel.

Column 1104 corresponds to the condition in which a different twoconductive paths have shorted together to create chatter in the signalssensed by the corresponding two electrodes. Column 1104 corresponds to ashort circuit between the RV shocking coil and one of the RV ring andthe RV tip. When the method of FIG. 12 determines that a short circuitedcondition has occurred between the RV shocking coil and the RV ring orRV tip, the method determines the result in the cell 1161. Cell 1161indicates that, when a short between two conductive paths causes thetype 1 and (type 2 or type 3) failures, then the method will determinethat the third (SVC far-field bipolar) channel detects a different ratethan the second (integrated bipolar) and first (bipolar) channels. Thecell 1161 also indicates that signals from the first and second channelscorrelate with one another. Cell 1165 indicates that more testing may beperformed.

Cell 1169 indicates that the method would declare the conductive paths,that are associated with the failure types 1 and (2 or 3) (e.g., a shortof the RV coil to the RV tip or RV ring), to be shorted together. Cell1173 indicates that the method would provide a clinical alert that apotential failure has occurred, and the method may instruct the IMD 100to switch to the RV coil to case electrode combination to performsensing and/or pacing. Cell 1177 indicates that the mitigation couldrepresent switching the sensing combination to the SVC coil-to-caseelectrode combination for sensing. Cell 1180 indicates that, if the SVCfar field bipolar channel exhibits a high rate, the IMD 100 shouldprovide a shocking stimulus, from the SVC coil to the case, as theSVC-case shock vector may be delivered regardless of the short betweenconductive paths.

Cell 1183 indicates that the clinical response should be to replace thelead, while cell 1187 indicates that the IMD 100 should continue to pacethrough the electrodes connected to the bipolar channel.

Column 1106 corresponds to the condition in which a third pair ofconductive paths have shorted together to create chatter in the signalssensed by the corresponding electrodes. Column 1106 corresponds to ashort circuit between the SVC shocking coil and one of the RV ring andthe RV tip. When the method of FIG. 12 determines that a short circuitedcondition has occurred between the SVC shocking coil and the RV ring orRV tip, the method determines the result in the cell 1162. Cell 1162indicates that, when a short between two conductive paths causes thetype 4 and (type 2 or type 3) failures, then the method will determinethat the second (integrated bipolar) channel detects a different ratethan the third (SVC far-field bipolar) and first (bipolar) channels. Thecell 1162 also indicates that signals from the first and third channelscorrelate with one another. Cell 1166 indicates that more testing may beperformed.

Cell 1170 indicates that the method would declare the conductive paths,that are associated with the failure types 4 and (2 or 3) (e.g., a shortof the SVC coil to the RV tip or RV ring), to be shorted together. Cell1174 indicates that the method would provide a clinical alert that apotential failure has occurred. Cell 1178 indicates that the mitigationcould represent switching the sensing combination to the RV coil-to-caseelectrode combination for sensing. Cell 1181 indicates that, if theintegrated bipolar channel exhibits a high rate, the IMD 100 shouldprovide a shocking stimulus, from the RV coil to the case, as theRV-case shock vector may be delivered regardless of the short betweenconductive paths.

Cell 1184 indicates that the clinical response should be to replace thelead, while cell 1188 indicates that the IMD 100 should continue to pacethrough the electrodes connected to the bipolar channel.

FIG. 12 illustrates a process 1200 for detecting potential combinationsor pairs of lead or channel failures of the IMD 100 (shown in FIG. 1)within the sensing subsystem 800 shown in FIG. 8. The process 1200represents a lead failure detection scheme for implanted leads, wherethe process 1200 utilizes simultaneous sensing over at least threechannels to detect shorts between conductors. The pairs of lead orchannel failures may arise in connection with temporary or permanentfailures in which conductive paths of two or more electrodes becomeshorted together, where the two electrodes are used in connection withtwo sensing channels. For example, the conductive wires creating theconductive paths of any two or more of the SVC shocking coil, RAelectrode, RV shocking coil, RV ring, RV active fixation helix, LA coilelectrode, LA ring electrode, LV coil electrode, LV ring electrode, LVtip electrode and the like, may be shorted together. When the conductivepaths for two or more electrodes short together, then the differentialsignals associated with the two or more faulty electrodes are affected.The operations of FIG. 12 detect and respond to faults arising fromfailures that affect two or more electrodes. FIG. 12 will be discussedin connection with the table of FIGS. 11A and 11B regarding failuresaffecting two or more electrodes (or two or more sensing channels).

The operations illustrated in FIG. 12 are performed following thedecision at 904 in FIG. 9. The operations in FIG. 12 are also performedfollowing the decision in FIG. 9 at 908. The decisions at 904 and 908 inFIG. 9 may determine that the rates associated with at least two signalsfrom the first, second and third signals are not similar (904) and/orare not physiologic (908). At points 905 and 909 in FIG. 9, the processbranches along parallel paths. One path is illustrated in FIG. 9 anddiscussed above in connection with FIGS. 10A and 10B. The alternativeparallel path is described hereafter in connection with FIGS. 11A and11B and 12.

In FIG. 12, at 1202, the sensed signals are obtained from memory for thefirst, second and third channels (similar to the operation at 912 inFIG. 9). At 1204, the sensed signals over the first, second and thirdchannels are analyzed for characteristics indicating whether suchsignals are physiologic or non-physiologic, such as the rate, slew rate,amplitude and the like as discussed above.

At 1206, it is determined whether only two of the sensed signals exhibitnon-physiologic waveforms, while a third sensed signal exhibits aphysiologic waveform. When none, one or three of the signals exhibitnon-physiologic waveforms, flow moves along the branch denoted N back topoint B in FIG. 9. When all three signals are non-physiologic, this isan indicator that the electrode common to all three signals has failed,which is addressed in FIG. 9. When flow branches along the path denotedN, this is a determination that there is little or no risk that twoelectrodes have shorted with one another. Hence, the concerns ofelectrode points shorting together as discussed above in connection withFIGS. 11A and 11B would not occur. Alternatively, at 1206, when twochannels exhibit non-physiologic waveforms and a third signal exhibits aphysiologic waveform, then the potential exists that electrodesassociated with different channels have short-circuited together. Hence,flow moves along the branch denoted Y to 1208.

At 1208, the method determines whether the second and third signalsexhibit non-physiologic waveforms. When the second and third signalsexhibit non-physiologic waveforms, flow moves to 1212 where the processdeclares failure 1 and 4 to represent a short circuit condition betweenthe associated electrodes that are distinct and unique to the second andthird signals. As explained above, the first, second and third channelsmay utilize a common electrode and also utilize unique correspondingelectrodes. When the second and third sensed signals are bothrepresentative of the potential failure, but the first sensed signalrepresents a physiologic waveform, at 1208 the method declares thesecond and third channels to have distinct and unique electrodes thatare in a short circuit state with one another. The declaration at 1212corresponds to the cell 1168 discussed above in connection with FIGS.11A and 11B.

At 1214, the method performs an alert and mitigation in connection withthe operations discussed above in FIGS. 11A and 11B regarding cells1172, 1176, 1178, 1182 and 1186. Thereafter, flow returns to point B inFIG. 9.

Returning to 1208, when the method determines that the second or thirdsignals exhibits a physiologic signal, flow moves along the branchdenoted N to 1209. At 1209, the method determines whether the first andsecond signals exhibit non-physiologic waveforms. When the first andsecond signals exhibit non-physiologic waveforms, flow moves to 1216where the method declares a failure of the RV coil to tip or RV to RVring short circuit. For example, when the first and second sensedsignals are both representative of the potential failure, but the thirdsensed signal represents a physiologic waveform, at 1216 the methoddeclares the first and second channels to have electrodes that are in ashort circuit state with one another. The declaration at 1216corresponds to cell 1169 in FIGS. 11A and 11B. Next, at 1218, the methodperforms an alert and mitigation operation such as in connection withthe operations described at cells 1173, 1177, 1180, 1183 and 1187 inFIGS. 11A and 11B. Thereafter, flow returns to point B in FIG. 9.

Returning to 1209, when one of the first and second signals exhibit aphysiologic waveform, flow moves along the branch denoted N to 1210. At1210, the method determines whether the first and third signals exhibitnon-physiologic waveforms. When the first and third signals exhibitnon-physiologic waveforms, flow branches along the path denoted Y to1220 where the method declares a failure of the SVC to tip or SVC toring short circuit. When the first and third sensed signals are bothrepresentative of the potential failure, but the second sensed signalrepresents a physiologic waveform, at 1220 the method declares the firstand third channels to have distinct and unique electrodes that are in ashort circuit state with one another. The declaration at 1220corresponds to cell 1170 in FIGS. 11A and 11B.

Next, at 1222, the method performs and alert and mitigation operationsuch as in connection with the operations described at cells 1174, 1778,1181, 1184 and 1188 in FIGS. 11A and 11B. Thereafter, flow returns topoint B in FIG. 9.

When the processes of FIGS. 9 and 12 both declare faults, but declaredifferent fault types, the fault declared in FIG. 12 may be affordedpriority and acted upon. Alternatively, the faults declared in FIGS. 9and 12 may both be considered to arrive at an alert and mitigationcourse of action.

FIG. 13 illustrates a sensor subsystem 1300 formed in accordance with analternative embodiment. The sensor subsystem 1300 may be used in placeof the sensing amplifiers 268 and 270 in FIG. 2. The sensor subsystem1300 is similar to the subsystem 800 in FIG. 8, except for the inclusionof a multiplexer switch 1302 in place of the third SBSA amplifier 802.The subsystem 1300 includes an integrated bipolar sensing amp 1304 and abipolar sensing amp 1306. One input 1308 of the integrated bipolarsensing amp 1304 is coupled to the output of the multiplexer switch1302. The inputs of the multiplexer switch 1302 are coupled to twodifferent electrodes, such as the SVC shocking coil and the RV shockingcoil. Alternative electrodes may be coupled to the multiplexer switch1302.

The inputs of the bipolar sensing amp 1306 are coupled to twoelectrodes, such as an RV ring electrode and an RV tip electrode.Optionally, the integrated bipolar sensing amp 1304 may include a secondinput 1310 that is coupled to a common electrode as one of the inputs tothe bipolar sensing amp 1306 (e.g., RV tip).

In accordance with the embodiments described herein, methods and systemsare provided for discriminating an open or a short circuit, identifyingthe location of the open or short circuit, warning the patient orphysician, and allowing the IMD to mitigate the problem byself-reprogramming when such mitigation is available.

In accordance with embodiments described herein, methods and systems areprovided for determining when an insulation failure occurs at specificlocations, such as 1) any conductor (tip, ring, RV coil, SVC coil) mayshort intermittently to the can, 2) the tip or ring may shortintermittently to the RV coil and 3) the tip, ring, or RV coil may shortto the SVC coil.

In accordance with embodiments described herein, methods and systems areprovided to: 1. Detect lead fracture; 2. Determine where the leadfracture is located; 3. Provide a warning to the clinician managing thepatient and/or potentially the patient of the lead failure; 4. Providean automatic response to mitigate the lead fracture and thus permit thesystem to continue operating to protect the patient; and 5. Respond inthe event of a catastrophic failure by alerting the clinician and letthe clinician know the nature of the failure (thereby helping theclinician protect the patient until the lead can be replaced).

It is noted that electrograms (IEGM) measured between electrodes thatare stationed inside the heart are generally free of myopotentials(e.g., electrical signals arising in the skeletal musculature which maybe sensed and falsely interpreted as a depolarization event). By usingIEGM signals, the methods and systems reduce the possibility thatmyopotentials will confound any detection or analysis operationsdescribed herein. Myopotentials have lower slew rates than chatterpotentials. By measuring the slew rates, the methods and systems hereincan identify the source of the high frequency noise: myopotentials orchatter.

In certain embodiments, the methods and systems perform single faultdetection by processing one fault at a time. Once a fault is detectedand mitigated, the methods and systems may continue to operate on asingle fault detection basis. Optionally, the methods and systems may beutilized to deal with multiple simultaneous faults. For instance, themethods and systems may be utilized to deal the condition in which afirst time incidence of lead chatter occurs at exactly the same time asa “shockable” arrhythmia. While simultaneous faults are not very likely,the methods and systems may detect the faults.

In certain embodiments, the methods and systems use concurrent sensingalgorithms using the bipolar channel (between tip and ring) and one ormore steerable sensing channels. Bipolar sensing between the tip andring (BS) may be used for arrhythmia detection. Sensing between the tipand RV coil represents integrated bipolar sensing (IBPS) and may be usedfor arrhythmia detection. Finally, sensing between the tip to SVC coil(IBPS-SVC) is capable of detecting arrhythmias but further signalfiltering may be desirable to avoid interference from sensedmyopotentials.

Noise associated with lead failure is caused by rapidly making andbreaking contact at wire fracture sites or shorting between conductors.Optionally, the recorded signals may be stored for future review andpost processed to verify that transient signals exhibited high amplitudeand slew rate. Transient signals exhibiting high amplitude and slew ratevalidate such signals to be likely make/break signals and notmyopotentials.

Alternatively an impedance plethysmography circuitry may be turned onimmediately upon detection of suspected high amplitude transients sensedover one or more sense channel. Lead fractures can then be verifiedthrough detection of high impedance signals even when a sensed signalexhibits a very short make/break event. The impedance plethysmograph hasa multiplex unit that allows for steering current to any pair ofelectrodes while detecting the voltage between any pair of electrodes.

In certain embodiments, the methods and systems use concurrent sensingalgorithms for bipolar sensing (BPS) and a steerable sensing channelthat may be switched between the RV coil and tip (IBPS) or the SVC coiland tip (IBPS SVC). BPS and SSRV coil configurations are clinicallyacceptable and the sensing algorithms can run in parallel using the samelogic. Also, the BPS and SSRV coil configurations are not likely to becorrupted by myopotentials that can be misclassified as VT/VF.

In certain embodiments, if high rate events occur simultaneously on bothchannels and these events are in a “physiologic rate range,” then afinal check may be performed to verify IEGMs are deemed as physiologicIEGMs. When the IEGMs are physiologic, then the events are deemed as“shockable.”

In certain embodiments, if high rate events occur on only one channelwhile the other channel indicates much lower rate, then the event may bedeemed as non-shockable. The event is stored and used to warn thephysician and patient of lead failure. In addition depending on whichelectrode displays the failure a determination of the fault can beachieved and the system can eliminate that electrode from the arrhythmiasensing circuit, with another electrode pair potentially being used inplace thereof.

In certain embodiments, if the failure is localized as being on theshocking coil, the system may be deemed as inoperable and the leadshould be replaced.

It is to be understood that the above description is intended to beillustrative, and not restrictive. For example, the above-describedembodiments (and/or aspects thereof) may be used in combination witheach other. In addition, many modifications may be made to adapt aparticular situation or material to the teachings of the inventionwithout departing from its scope. While the dimensions and types ofmaterials described herein are intended to define the parameters of theinvention, they are by no means limiting and are exemplary embodiments.Many other embodiments will be apparent to those of skill in the artupon reviewing the above description. The scope of the invention should,therefore, be determined with reference to the appended claims, alongwith the full scope of equivalents to which such claims are entitled. Inthe appended claims, the terms “including” and “in which” are used asthe plain-English equivalents of the respective terms “comprising” and“wherein.” Moreover, in the following claims, the terms “first,”“second,” and “third,” etc., are used merely as labels, and are notintended to impose numerical requirements on their objects. Further, thelimitations of the following claims are not written inmeans-plus-function format and are not intended to be interpreted basedon 35 U.S.C. §112, sixth paragraph, unless and until such claimlimitations expressly use the phrase “means for” followed by a statementof function void of further structure.

This written description uses examples to disclose the invention,including the best mode, and also to enable any person skilled in theart to practice the invention, including making and using any devices orsystems and performing any incorporated methods. The patentable scope ofthe invention is defined by the claims, and may include other examplesthat occur to those skilled in the art. Such other examples are intendedto be within the scope of the claims if they have structural elementsthat do not differ from the literal language of the claims, or if theyinclude equivalent structural elements with insubstantial differencesfrom the literal languages of the claims.

What is claimed is:
 1. A method for detecting potential failures by animplantable medical lead, comprising: sensing first, second and thirdsignals between at least first and second combinations of electrodes, onthe lead; determining whether at least one of the first, second andthird signals is representative of a potential failure in the lead;correlating two or more of the first, second and third signals that arerepresentative of a potential lead failure with one another; andidentifying a failure and one or more electrodes associated with thefailure based on which of the first, second and third sensed signals isrepresentative of the potential failure and the correlation between thesignals representative of the potential failure.
 2. The method of claim1, further comprising: when only two signals of the first, second andthird sensed signals are both representative of the potential failure,while a third signal of the first, second and third sensed signals isphysiologic, determining which two electrodes are distinctly associatedwith the two signals representing potential failure; and declaring ashort between the two electrodes.
 3. The method of claim 1, wherein thefirst, second and third channels utilize a common electrode, the methodfurther comprising: when the first and second sensed signals are bothrepresentative of the potential failure and when the third sensed signalrepresents a physiologic waveform, declaring the first and secondchannels to have electrodes that are in a short circuit state with oneanother.
 4. The method of claim 1, wherein the sensing comprises sensingthe first and second signals over a common channel associated with thefirst combination of electrodes at successive different first and secondpoints in time.
 5. The method of claim 1, further comprising disablingsensing over at least one of the first and second channels that isassociated with the failure, and enabling a different third channel tosense signals from a third combination of electrodes.
 6. The method ofclaim 1, wherein the sensing comprises sensing the first, second, andthird signals over first, second and third channels betweencorresponding combinations of the electrodes.
 7. The method of claim 6,wherein the first combination of electrodes includes a ring electrodeand a tip electrode, the second combination of electrodes includes acoil electrode and the tip electrode, and the third combination ofelectrodes includes the tip electrode and an SVC electrode.
 8. Themethod of claim 1, further comprising declaring a failure of first andsecond electrodes of the first and second combinations when the firstand second signals are representative of non-physiologic signals.
 9. Themethod of claim 1, further comprising declaring a short circuit statebetween first and second electrodes when the first and second signalsare both representative of non-physiologic signals.
 10. An implantablemedical device (IMD), comprising: at least one lead configured to bepositioned within a heart and including at least first and secondcombinations of electrodes that sense first, second and third signals; achannel selection module configured to control which of the electrodesare included in the at least first and second combinations ofelectrodes; and a failure detection module configured to determinewhether at least one of the first, second and third signals arerepresentative of a potential failure in the lead, and to correlate twoor more of the first, second and third signals that are representativeof a potential lead failure with one another, the failure detectionmodule being further configured to identify a failure and one or moreelectrodes associated with the failure based on which of the first,second and third sensed signals are representative of the potentialfailure and the correlation between the signals representative of thepotential failure.
 11. The device of claim 10, wherein the failuredetection module identifies a tip electrode to be associated with thefailure when the first and second signals are correlated with oneanother and are representative of non-physiologic signals.
 12. Thedevice of claim 10, wherein the failure detection module compares atleast one of an amplitude, a rate and a slew rate of the first andsecond signals to a predetermined threshold representative of aphysiologically acceptable limit for the corresponding one of theamplitude, rate and slew rate.
 13. The device of claim 10, wherein thechannel selection module is configured to enable a different fourthchannel to sense cardiac signals from a fourth combination of electrodeswhen a failure is identified by the failure detection module.
 14. Thedevice of claim 10, wherein the channel selection module is configuredto disable sensing over a one of the first and second channels thatutilizes an electrode associated with the failure.
 15. The device ofclaim 10, wherein the failure detection module is configured to declarea failure of first and second electrodes of the first and secondcombinations when the first and second signals are representative ofnon-physiologic signals.
 16. The device of claim 10, wherein the failuredetection, module is configured to declare a short circuit state betweenfirst and second electrodes when the first and second signals are bothrepresentative of non-physiologic signals.
 17. The device of claim 10,further comprising a sensor subsystem configured to sense the first andsecond signals over a common channel associated with the firstcombination of electrodes at successive different first and secondpoints in time.
 18. The device of claim 10, further comprising a sensorsubsystem configured to sense the first, second, and third signals overfirst, second and third channels between corresponding combinations ofthe electrodes.
 19. The device of claim 10, wherein the first, secondand third channels utilize a common electrode, and wherein the failuredetection module is configured, to when the first and second sensedsignals are both representative of the potential failure and when thethird sensed signal represents a physiologic waveform, to declare thefirst and second channels to have electrodes that are in a short circuitstate with one another.